Electronically controlled prosthetic system

ABSTRACT

A prosthetic joint system for users comprising a housing having an interior cavity, a center axis in said interior cavity, and an attachment means for fixedly connecting said housing to said user; an inner cylinder disposed in said housing interior cavity wherein said inner cylinder rotates around said center axis of said housing; an appendage attached to said inner cylinder; a sensor system attached to said appendage; and a dampening system, having a power source, in communication with said sensor system, said inner cylinder, and said housing for controlling dampening of the rotation of said inner cylinder around said center axis of said housing.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. Ser. No. 15/689,838, filed onAug. 29, 2017, currently pending, which is a continuation of U.S. patentapplication Ser. No. 15/092,231, filed Apr. 6, 2016, now U.S. Pat. No.9,775,726, issued on Oct. 3, 2017, which is a continuation-in-part ofU.S. patent application Ser. No. 14/221,457, filed Mar. 21, 2014, nowabandoned, which is a continuation-in-part of U.S. patent applicationSer. No. 13/351,291, filed Jan. 17, 2012, now abandoned, which is acontinuation of U.S. patent application Ser. No. 12/979,434, filed Dec.28, 2010, now abandoned, which is a continuation of U.S. patentapplication Ser. No. 12/185,907, filed Aug. 5, 2008, now abandoned,which is a continuation-in-part of U.S. patent application Ser. No.11/953,390, filed Dec. 10, 2007, now abandoned, which is a continuationof U.S. patent application Ser. No. 11/801,790, filed May 11, 2007, nowabandoned, which is a continuation-in-part of U.S. patent applicationSer. No. 11/343,066, filed Jan. 30, 2006, now U.S. Pat. No. 7,393,364,issued Jul. 1, 2008, which is a continuation of U.S. patent applicationSer. No. 10/410,491, filed Apr. 9, 2003, now U.S. Pat. No. 7,029,500,issued on Apr. 18, 2006, which is based on U.S. Provisional ApplicationSer. No. 60/371,974, filed on Apr. 12, 2002. The entire content of eachof the above-referenced applications is hereby expressly incorporatedherein by reference.

FIELD OF THE INVENTION

The present invention relates generally to an ankle and foot jointsystem. More particularly, the present invention is a new and improvedprosthetic joint system, which simulates natural human locomotion, andhuman biomechanics through sensory feedback, time feedback,electronically controlled dampening joint assembly, and a microprocessorcontrol system.

BACKGROUND OF THE INVENTION

As the study of human physiology and anatomy clearly demonstrates, therelative simple action of walking on an even flat surface involvesnumerous biomechanical complexities. A single step requires constantbiofeedback such as continual analysis of proprioception, angulations,timing, and balanced muscular-skeletal functions. In the prior art, theprosthetic industry is continuously attempting to mimic natural humanlocomotion (NHL), performance and aesthetics.

The field of prosthetics, in general, has made enormous advances inimproving amputee and congenitally deformed individuals' performance onmultiple levels from general ambulation to competitive sports throughimproved technology and understanding of human biomechanics. Although,it is known in the art to manufacture ankle and foot prostheticcombinations that have generally increased performance and appearance,the prior art is still deficient on numerous levels as will be discussedin greater detail below.

Many prosthetic feet are optimized for a small or limited range ofactivities. Typically, models aligned for such activities as dailywalking are not optimally aligned for running and vice versa. It is,therefore, desirable to provide a design that allows a user to go fromwalking to running to provide greater user flexibility in multipleactivities. Furthermore, while prior art prosthetic devices may havegenerally moved amputees toward more biomechanically appropriate gaitpatterns, current mechanically controlled designed prosthetic feet donot allow for significant alterations in gait speed without losingoptimal biomechanical characteristics essential with walking or running.Still furthermore, it is desirable to provide a design that allowstransition from flat ground to moving up hill or from flat ground tomoving downhill with ease, safety, function, and generally traversinguneven surfaces, where the prior art is lacking.

There are models in the prior art that are characterized by the termENERGY STORING that may provide greater energy return than other modelsthrough spring-return characteristics of the keel members to lessenenergy expenditures. Additionally, models that provide MULTI-AXIALuneven ground accommodation have been developed to better assist usersto gain better balance on real-world environments. Unfortunately,neither of these categories of advancements provides both optimal energyreturn and uneven ground accommodation sufficiently to meet user needsin all activities and in all environments. While numerous prostheticfeet and ankle systems are available in the market, no mechanical basedprosthetics provide full mimicking of their anatomical counterpart. Itis now contemplated that optimal biomechanical and natural humanlocomotion functions cannot come solely through a relative simplemechanical device such as found in much of the existing prior art.

By example in non-ankle and foot prosthetics, it has been observed in amicroprocessor controlled C leg knee design by the company OTTO BOCKthat amputees are able to have better gait symmetry, decreased energyexpenditure, and a much greater sense of mental confidence in ambulatingthan non-microprocessor prosthetic knees, however, there remains asignificant gap between the most advanced prosthetics and the humanbody. Therefore, there remains a need to greatly improve the functionalabilities of the prosthetic system, and hence, the abilities of theamputee. It is now contemplated that similar benefits could be observedthrough this type of design but for a broader spectrum of amputees,including trans-tibial amputees, through the use of a computercontrolled prosthetic ankle and foot system with appropriate sensoryfeedback mechanisms. Through this disclosure, an improved prostheticcontrol system is discussed which more closely mimics the naturalcontrol functions of the human body.

Another consideration lacking in the prior art of ankle and foot devicesis the combination of aesthetics and function. It is desirable toprovide a prosthetic foot that also has a much more cosmetic effectthrough better simulating proper natural human locomotion and allows thefoot to plantarflex during sitting to better simulate a real ankle andfoot. In this manner, a user's foot and ankle would appear more normalthan the telltale sign of a prosthetic that juts unnaturally up whensitting.

Oftentimes, aesthetics is sacrificed for increased function. A commoncomplaint of many prosthetic foot users, for instance is that theirprosthetic foot “sticks up” with unnatural dorsiflexion angle when theysit. This remains a problem due to the prior art prosthetic feet beingrelatively affixed at a given angle with respect to the prosthesis,thus, during sitting the foot remains pointing upwards as the shinsection of the prosthesis has a posterior lean when the amputee issitting. This is a major complaint of many prosthetic users, and has notbeen adequately addressed through commercially available prosthetics.

The OSSUR Proprio Foot design does allow for plantarflexion duringsitting, however, it is does not take place in an aesthetically naturalmanner. After a few moments after sitting, the foot then plantarflexesthrough powered actuation. The design disclosed in this patent has theability to naturally, and immediately plantarflex during sitting,accommodating for the natural angle of the shin with respect to theground.

With robotics and advanced prosthetics, it is essential that the motionof the bio-replicating design match the natural movement of theanatomical counterpart in great detail. As the realistic nature of theprosthesis approaches that of the natural limb, in cosmetic physicallyand biomechanically similar characteristics, the psychologicalacceptance of the device becomes increasingly difficult. When abio-resembling robotic device or advanced prosthesis offers enoughdissimilarities from the natural limb, the psyche recognizes that it isnot real and readily accepts the device, though the prosthetics user isoften dissatisfied with the capabilities of the device by notreplicating the body well enough. When the robotic or prosthetic device,however, approaches the upper limits of realism, a psychological effectreferred to as the “Uncanny Valley” syndrome occurs, resulting in theuser's dissatisfaction with the device, though it is more life-like thanless biomechanically similar counterparts. It is imperative that therealistic nature of the advanced design illustrated here is capable ofbeing fine-tuned to the natural movement of the user, in all conditionsand in all environments, whereas to allow for full mental acceptance ofthe design being integrated as an accessory extension of the body. Thisdisclosed design, unlike other prosthetics available in the field today,offers much more life-like appearance than conventional technology, suchas in plantarflexion during sitting, and allows for fine-tunedadjustments of the movement to prevent the Uncanny Valley syndrome withrespect to prosthetic acceptance.

Furthermore, the stubbing of a prosthetic foot has proven to be a safetyissue for trans-tibial, trans-femoral, and hip-disarticulation amputeesalike at all activity levels. This often occurs because manyconventional prosthetic feet do not dorsiflex during the swing phase ofgait, as occurs naturally. The prior art prosthetic feet have attemptedto dorsiflex the foot during swing phase in the past, such as with the aprior art design under the trademark or name HYDROCADANCE, but havegenerally failed to provide the full range of benefits desired, such asbeing able to be used on a vast array of lower extremity amputees'functional abilities and amputation levels as well as provide optimalenergy return characteristics, range of motion, and a life-likeappearance, to name a few. The OSSUR Proprio Foot does allow fordorsiflexion during the swing phase of gait, but is unable toappropriately accommodate for the necessary dorsiflexion anglecorrelating to the terrain angle. Additionally, its dorsiflexionability, and other movement characteristics, takes place over a seriesof steps, but does not occur in real-time, as this design does.

Still furthermore, it is desirable to have a functional prosthetic thatmay also allow a user to choose from various cosmetically shaped footshells where the prior art fails. Though prosthetic feet are notcommonly seen because they are frequently covered by shoes, cosmeticappearance is a very important aspect to many amputees and other usersdue to current lifestyle and fashion trends. It is therefore desirableto provide a device that may allow several foot shell templates tochoose from or to have customized foot shell molds fabricated much likewhat is now available with upper extremity prosthetics cosmetic gloves.

What is needed is a prosthetic design utilizing electronics such as butnot limited to a prosthetic microprocessor, sensory feedback mechanismsfor various angle, time, and moment or pressure sensors, and activelyproviding a means for adjusting plantarflexion and dorsiflexion throughprosthetic proprioception which will allow a user to transverse allnecessary barriers with appropriate biomechanical precision, stability,and range of activities.

Furthermore, it is desirable to provide a design for a very active userwho may want to perform daily activities and run, and which providesadditional stability and safety for lower activity users who simply needto traverse low level barriers with enhanced safety and stability.

Still furthermore, one of the areas of prosthetics that is very much atits infancy stages is creating prosthetic sensory feedback mechanisms.It is believed that the better the mesh between the human and machineinteractions, the more functional, safe, and life-like a user'sabilities will become.

Currently found in prosthetic systems used today or in prostheticresearch laboratories is the sense of feel system which generallyattempts to correspond to human tactile receptors in extremities. Theprosthesis detects pressure and stimulates the residual limb in a mannerto trick the brain into thinking it is “feeling” with the prosthesisthrough cerebral projections. In essence, the prosthesis attempts tocommunicate or provide feedback to the user's brain.

Furthermore, there is also myoelectric control, which generally attemptsinteraction from muscular control of extremity muscles. The electricalactivity from the muscular actions within the residual limb is picked upby electrodes embedded in, by example, the socket system and cause theprosthetic hand to move in an intended manner. In essence, the brainattempts to communicate or provide feedback to the prosthesis.

Still furthermore, it is understood to attempt a general prostheticbrain wherein correspondence to a sort or proprioception by having themicroprocessor embedded in the prosthesis, along with an array ofvarious sensors, cause the prosthetic joint to move in a fashion thatmatches up to the wearer's gait pattern and/or intended movement. Byexample in the prior art, the C-leg system uses a microprocessor orprosthetic brain to constantly analyze how fast it should flex andextend during the swing phase of gait, as well as how much stancestability to maintain during the stance phase of gait, amongst otheractions. Such design generally mimics the motion of the sound limbindependent of the terrain or slope, according to a pre-set determinedset of variables. While this design does adjust its stance and swingcharacteristics, it does not provide do so in accordance with theanatomical limb's natural movement in all conditions and in allenvironment, and not in a full bio-replicating manner.

Although prosthetic technology has advanced in recent years, the priorart still has failed to bridge the gap between man-made prosthetics anduser demand and needs. Likewise, there is also a desire to enhance thebody/prosthesis integration through sensory feedback mechanisms andprosthetic proprioception. Therefore, an extensive opportunity fordesign advancements and innovation remains where the prior art fails oris deficient.

SUMMARY OF THE INVENTION

In general, the present invention is a new and improved prosthetic jointsystem which provides natural human locomotion and aesthetics where theprior art fails. The present invention generally provides a sensory andtime feedback system that works in conjunction with a self-containedmicroprocessor to control and regulate a dampening system for a jointassembly that utilizes but is not limited to magnetorheological fluid,hydraulic fluid, oil, water, or saline solution, or other controllablefluid.

Without the intention of limitation, the invention may generally becomprised of a prosthetic foot, foot and ankle, or ankle unit, as wellas having the inclusion of other joints such as but not limited to theknee and hip joints. Additionally, without the intention of limitation,the invention may generally comprise a keel being fixedly attached to aninner or outer cylinder. The inner or outer cylinder is generallydisposed in a rotational manner to the other cylinder or housing whichin turn is fixedly attached to a user's lower extremity. It isunderstood that the term cylinder may encompass a virtual arc segmentabout a fixed or moving axis, and should not be considered limiting. Theinner cylinder rotation is generally controlled by a dampening systemthat may utilize magnetorheological, hydraulic, or other fluid thatreceives input from a microprocessor in communication with the sensors.The sensors that are used to provide information to the microprocessormay be located on the keel, brackets, damper, pylon, or otherembodiments of the device. These sensor systems provide information asto the desired or intended movement for the control of the device.

In this respect, before explaining at least one embodiment of theinvention in detail, it is to be understood that the invention is notlimited in this application to the details of construction and to thearrangement of the components set forth in the following description orillustrated in the drawings. The invention is capable of otherembodiments and of being practiced and carried out in various ways.Also, it is to be understood that the phraseology and terminologyemployed herein are for the purpose of description and should not beregarded as limiting. As such, those skilled in the art will appreciatethat the conception, upon which this disclosure is based, may readily beutilized as a basis for the designing of other structures, methods andsystems for carrying out the several purposes of the present invention.It is important, therefore that the claims be regarded as including suchequivalent constructions insofar as they do not depart from the spiritand scope of the present invention.

Accordingly, titles, headings, chapters name, classifications andoverall segmentation of the application in general should not beconstrued as limiting. Such are provided for overall readability and notnecessarily as literally defining text or material associated therewith.

Further, the purpose of the foregoing abstract is to enable the U.S.Patent and Trademark Office and the public generally, and especially thescientists, engineers and practitioners in the art who are not familiarwith patent or legal terms or phraseology, to determine quickly from acursory inspection the nature and essence of the technical disclosure ofthe application. The abstract is neither intended to define theinvention of the application, which is measured by the claims, nor is itintended to be limiting as to the scope of the invention in any way.

It is therefore an object of the present invention to provide a new andimproved prosthetic joint system, and more particularly, a prostheticankle and foot system with the possible inclusion of knee and hipjoints, that provides greater ease, safety, and function to a wide rangeof activities such as but not limited to moving from a walk to a run,transverse from flat ground to an uphill grade, or transverse from flatground to a downhill grade.

It should be understood as well that the prosthetic system in generalmay comprise a foot and ankle only, for users who have their anatomicalknee or who do not wish to utilize a more advanced knee unit.Furthermore, the system may comprise a foot and ankle and knee unit forthose users with the need for both a prosthetic foot and knee unit.Still furthermore, the system may comprise a foot and ankle and knee andhip units, all working on conjunction with each other for those userswho demand all these prosthetic joints of the leg due to a high level ofamputation. For purposes of simplicity of explanation, the system may bedescribed as foot, foot and ankle, or system, amongst other terms, butshould not be considered limiting to the specific joints mentioned. Itshould be further understood that the method of communication,interaction, and control of each of the joints offers distinctsimilarities and should therefore be considered in unison duringexplanation where applicable.

Additionally, it is an object of the present invention to provideaccommodation not only to slope alterations, but also to force and speedalterations as well.

It is a further object of the present invention to provide a new andimproved prosthetic joint system which is a relatively simple designwith few moving parts and thus may be easily and efficientlymanufactured.

An even further object of the present invention is to provide a new andimproved prosthetic joint system which is of a more durable and reliableconstruction than that of the existing known art.

Still another object to the present invention is to provide a new andimproved prosthetic joint system which is susceptible of a low cost ofmanufacture with regard to both materials and labor, which accordinglyis then susceptible of low prices of sale to the consuming public,thereby making such economically available to those in need of suchprosthetic devices.

Another object of the present invention is to provide a new and improvedprosthetic joint system which provides some of the advantages of theprior art, while simultaneously overcoming some of the disadvantagesnormally associated therewith.

Yet another object of the present invention to provide a new andimproved prosthetic joint system, and more particularly a prostheticankle and foot system that is well suited for most function level K2-K4amputees as well as benefit transtibial, transfemoral, hipdisarticulation amputees and, generally, all levels of lower extremityamputees.

Still yet, another object of the present invention is to provide a newand improved prosthetic ankle and foot system that generally utilizes akeel design wherein energy return is optimized and uneven ground is moreeasily traversed.

A further object of the present invention is to provide a new andimproved prosthetic ankle and foot system for multiple levels ofamputation and addresses issues of gait for all activity levels byallowing the foot to dorsiflex through swing phase of gait thus greatlyenhancing safety, decreasing mental anxiety, and increasing gaitsymmetry.

Still another object of the present invention is to provide a new andimproved prosthetic ankle and foot system that provides cosmetic effectthrough better simulating proper natural human locomotion, allowing thefoot to plantar flex during sitting, and features a more cosmeticallyshaped foot shell which may selectively be chosen from a variety ofstyles.

Another object of the present invention is to provide a new and improveddampening mechanism for artificial joints comprising MR fluid or otherfluidly characterized system. The mechanism may be utilized on otherprosthetic or orthotic joint systems. Furthermore, the mechanism mayallow for retrofitting to prior art, readily available prosthetic feetand ankle joints.

An even further object of the present invention is to provide a new andimproved prosthetic joint system, which may provide instantaneouscommunication from the prosthesis to the user wherein feedback isprovided such that a sense of spatial and angular orientation of theprosthetic joint is achieved, as well as a sense of resistance to thatangular change.

Still further, an object of the present invention is to provide a newand improved prosthetic joint system wherein instantaneous communicationfrom the user to the prosthesis is achieved for better regulating,controlling, or positioning the prosthesis.

These together with other objects of the invention, along with thevarious features of novelty, which characterize the invention, arepointed out with particularity in the claims annexed to and forming apart of this disclosure. For a better understanding of the invention,its operating advantages and the specific objects attained by its uses,reference would be had to the accompanying drawings and descriptivematter in which there are illustrated preferred embodiments of theinvention.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a partial cut away side view of a preferred embodiment of theinvention.

FIG. 2 is a partially exploded perspective view of a preferred generalconstruction in accordance with the present invention.

FIG. 3 is a side view of a preferred construction of a keel inaccordance with the present invention also generally showing a naturalweight line.

FIG. 3A is a top view of a preferred general construction of a keel anda bracket assembly in accordance with the present invention also showingthe intersection of the weight line.

FIG. 4 is a side view of a preferred general construction of a jointassembly in accordance with the present invention.

FIG. 4A is a partially exploded perspective view of a preferred generalconstruction of an outer cylinder in accordance with the presentinvention.

FIG. 4B is a side view of a preferred general construction of an outercylinder in accordance with the present invention.

FIG. 4C is a partially exploded perspective view of a preferred generalconstruction of an outer cylinder in accordance with the presentinvention.

FIG. 4D is another side view of a preferred general construction of anouter cylinder in accordance with the present invention.

FIG. 5 is a side view of a preferred general construction of an innercylinder in accordance with the present invention.

FIG. 5A is a partially exploded perspective view of a preferred generalconstruction of an inner cylinder in accordance with the presentinvention.

FIG. 5B is a side view of a preferred general construction of an innercylinder in accordance with the present invention.

FIG. 5C is a partially exploded perspective view of a preferred generalconstruction of an inner cylinder in accordance with the presentinvention.

FIG. 5D is another side view of a preferred general construction of aninner cylinder in accordance with the present invention.

FIG. 6 is a side view of a preferred general construction of a shaft inaccordance with the present invention.

FIG. 6A is a perspective view of a preferred general construction of ashaft in accordance with the present invention.

FIG. 6B is another side view or end view of a preferred generalconstruction of a shaft in accordance with the present invention.

FIG. 7 is a partial cross-sectional side view of a preferred generalconstruction of a joint assembly in accordance with the presentinvention and also generally depicting the horizontal.

FIG. 8 is a partial cross-sectional side view of a preferred generalconstruction of a joint assembly in accordance with the presentinvention and also generally depicting the MR fluid.

FIG. 8A is another partial cross-sectional side view of a preferredgeneral construction of a joint assembly in accordance with the presentinvention.

FIG. 9 is a partial cross-sectional top view of a preferred generalconstruction of a joint assembly conductive circuit in accordance withthe present invention.

FIG. 9A is a general illustration of a preferred embodiment inaccordance with the present invention.

FIG. 10 is a side view of a preferred general construction of a keel andbracket assembly in accordance with the present invention.

FIG. 10A is a perspective view of a preferred general construction of akeel and bracket assembly in accordance with the present invention.

FIG. 11 is general side view of a natural human foot also generallydepicting the natural weight line and rotation axis of an anatomicalankle.

FIG. 11A is general side view of a natural human foot generallydepicting the natural weight line, rotation axis of an ankle, and apreferred placement of a keel with MR dampening system center ofrotation generally matching up to anatomical center of rotation as wellas keel design mimicking the anatomical skeletal plantar surface of thefoot in accordance with a preferred construction of the invention.

FIG. 11B is general side view of a natural human foot generallydepicting the rotation axis or point of a human ankle.

FIG. 12 is a general illustration of a flow chart depicting elements ofcontrol electronics in a preferred construction of the invention.

FIG. 12A is a sketch or schematic representation generally depicting apreferred embodiment of the invention wherein sensory feedback issupplied from the invention to a user.

FIG. 12B is a sketch or schematic representation generally depicting apreferred embodiment of the invention wherein sensory feedback issupplied from the user to the invention.

FIG. 12C is a general illustration depicting elements of a natural humansystem for proprioception feedback pathway.

FIG. 12D is a general illustration of a flow chart depicting elements ofa natural human system for proprioception feedback pathway.

FIG. 12E is a general illustration of a flow chart depicting elements ofa system for proprioception feedback pursuant to a preferred embodimentof the invention.

FIG. 12F is a sketch or schematic representation generally depicting apreferred embodiment of the invention wherein sensory feedback issupplied from the invention to a user.

FIG. 12G is a general illustration of a flow chart depicting elements ofa system for proprioception feedback pursuant to a preferred embodimentof the invention.

FIG. 12H is a sketch or schematic representation generally depicting apreferred embodiment of the invention wherein sensory feedback issupplied from the invention to a user.

FIG. 13 is a general illustration depicting a preferred construction ofthe invention throughout gait cycle.

FIG. 14 is a graphical presentation showing general characteristics ofmagnetorheological fluid damper resistance during a gait cycle in apreferred construction of the invention.

FIG. 14A is a graphical presentation showing general characteristics ofnatural human muscle activity during a gait cycle.

FIG. 14B is a graphical presentation showing general characteristics ofnatural human muscle ankle angle during a gait cycle.

FIGS. 15A and 15B depict two embodiments of a two chamber system,comparing equivalency between them.

FIG. 16 is a general illustration depicting a two chamber damper withoffset axis of rotation with respect to the mechanical embodiment.

FIG. 17 is a general illustration depicting a two chamber damper withoffset axis of rotation with respect to the mechanical embodiment.

FIG. 18 is a general illustration depicting a two chamber damper.

FIG. 19 is a general illustration depicting a two chamber damper.

FIGS. 20A-C illustrate the use of a linear actuator to control aprosthetic system.

FIG. 21 is an exploded view of a damper mechanism used to convert rotaryto linear motion within a two chamber design.

FIGS. 22A and 22B illustrate two views of a damper mechanism used toconvert rotary to linear motion within a two chamber design.

FIG. 23A is a general illustration depicting a medial view of a keeldesign; and

FIG. 23B depicts a lateral view of the keel design.

FIG. 24 is a general illustration depicting proximal view of a keeldesign.

FIG. 25 is a general illustration depicting one embodiment of a valvedesign.

FIG. 26 is a general illustration depicting the various phases in thegait cycle.

FIG. 27 is a general illustration depicting one embodiment of blockdiagram of system electronics.

FIG. 28 is a general illustration depicting one embodiment of blockdiagram of system electronics and how they relate to the valve system.

FIG. 29 is a general illustration depicting one embodiment of blockdiagram of system.

FIG. 30 is a general illustration depicting pulse width modulation.

FIG. 31 is a general illustration depicting physiological sensoryfeedback loop and what is missing in conventional prosthetic systems.

FIG. 32 is a general illustration depicting a login page for a controlprogram.

FIG. 33 is a general illustration depicting a patient or userinformation page for a control program.

FIG. 34 is a general illustration depicting a resistance settings pagefor a control program, including possible adjustable variables,including but not limited to general plantarflexion angle experiencedduring midstance or other portion of the gait cycle.

FIG. 35 is a general illustration depicting an advanced settings pagefor a control system.

FIG. 36 is a general illustration depicting biomechanics dataillustrated within a control program of actual movement of the device inreal-time or past data.

FIG. 37 is a general illustration depicting further biomechanicsinformation that can be extracted from the device and displayed invarious means and methods.

FIG. 38 is a general illustration depicting further variables for abiomechanics data capturing system.

FIG. 39 is a general illustration depicting the ability to capturevideo, and video analysis of the user device's movement, which can beoverlaid or viewed with other biomechanics graphical and pictorialillustrations.

FIG. 40 is a general illustration depicting the ability to use virtualreality system in conjunction with the use of the device for trainingand control system, and system manipulation characteristics.

FIG. 41 is a general illustration of a sensory feedback tailoringsoftware system that can be used to refine the feedback to the userbased off of sensor information from the device and its function.

FIG. 42 is a general illustration of further control variables of asensory feedback system.

FIG. 43 is a general illustration depicting the relation of inner andouter cylinders for various illustrations of the same disclosureoverlaid.

FIG. 44 is a general illustration depicting an inner and outer cylinderequivalent in motion with two fluid chambers, an axis of rotation, andvalve system. This implementation offers equivalency to other depicteddesigns.

FIG. 45A and FIG. 45B are general illustrations depicting two fluidfilled compartments, an inner and outer cylinder equivalent in motionwith an axis of rotation, and valve system. FIG. 45A is a side view ofthe embodiment, and FIG. 45B is an end view.

FIG. 46 is a general illustration of a preferred embodiment inaccordance with the current invention.

FIG. 47 is a general illustration of a preferred embodiment inaccordance with the current invention.

FIG. 48 is a general illustration of a prior art braking system.

FIG. 49 is a general illustration of a prior art braking system.

FIG. 50 is a general illustration of a preferred embodiment inaccordance with the current invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Referring now to the drawings, wherein like reference numerals designatecorresponding structure throughout the views, and referring inparticular to FIGS. 1 and 2, reference numeral 10 generally refers to anew and improved prosthetic foot with ankle system, hereinafter referredto as prosthetic foot collectively, in accordance with the presentinvention. Invention 10 generally comprises keel 12, foot shell 14,ankle joint assembly 16, dampening means or system 18, a bracketassembly 20, sensor system 22, and attachment means 24. It should not beconsidered limiting what order certain components are depicted in theattached drawings. For instance, attaching either the inner or outercylinder to the keel should be considered to be within the scope of thesame invention, and does not depart from the intended disclosure. Itshould be understood that there are a number of orientations thatvarious components may be placed to provide a similar benefit to the enduser.

Furthermore, invention 10 is generally shown in a configuration for aright foot. It is understood that a left foot configuration isconsidered. It is further understood that invention 10 may be used onother joints and associated appendages such as but not limited to aknee, hip, elbow or others. The term appendages should not be consideredlimited to limbs such as arms and legs. Still furthermore, the termjoint generally refers to rotationally attached members. Stillfurthermore, the invention should not be considered limiting solely toprosthetics or orthotics applications, but should include anyanthropomorphic limb movement of robotic devices, as advancedprosthetics are anthropomorphic robots that work in conjunction with thehuman body.

Keel General Construction

Referring to the drawings and in particular FIGS. 3 and 3A, a preferredconstruction of keel 12 is generally depicted having a heel portion 26with posterior split 28 that generally separates the heel portion 26into a medial segment 30 and a lateral segment 32. Furthermore, keel 12further includes a forefront or toe portion 34 with anterior split 36that generally separates the toe portion 34 into a medial segment 38 andlateral segment 40. The area generally between heel portion 26 and toeportion 34 is generally referred to as middle portion 42 although it isunderstood that the term middle should not necessarily be construed asmeaning the actual middle point of keel 12.

It is further understood that a keel 12 may include the posterior split28 and/or anterior split 36 or neither. It is also understood thatanterior split 36 and posterior split 28 may run the full length of keel12 such that keel 12 is generally of a two piece construction (notdepicted). Furthermore, both anterior split 36 and posterior split 28are generally along the midline 44 of keel 12. It is understood thatgeneral split construction of keel 12 may generally improve ambulationover uneven ground among other beneficial ambulation.

In a preferred construction, anterior split 36 and posterior split 28should be of sufficient width 46, respectively, that a reasonable torqueon keel 12 should reduce or prevent toe portion 34 medial segment 38 andlateral segment 40 and heel portion 26 medial segment 30 and lateralsegment 32, respectively, from contacting or rubbing past the respectivesegments. Such construction may reduce or prevent a “clicking” noiseduring walking from said contact. It is also understood that rubber orother flexible material-based pieces (not depicted) may also be includedto reduce or prevent clicking and generally located in posterior split28 and/or anterior split 36.

The keel shape and dynamics are a vital component of the full and properfunctioning of the ankle joint. While the controllable functions andintelligent control system of the ankle joint can accommodate for variedtypes of keels, the system as a whole is best optimized with proper keelfunction and biomechanically similar characteristics. In a preferredembodiment, the keel may be highly compliant or highly non-compliant,and the ankle joints function should provide a smooth roll-over throughthe stance phase of the gait cycle, however, to fully replicate naturalbiomechanical movement with the greatest efficiency and natural feel, akeel designed with similar biosymmetrical shapes, compliance areas,roll-over characteristics, and physical segment proportions. Thesecharacteristics, as described herein, are meant to characterize thisgeneral embodiment with a certain degree of particularity. These are notmeant to be limiting to the disclosed characteristics only, but ratherto illustrate the highly anatomical replication that this keel designexhibits. This quality, of having a more highly anatomical replication,allows for this system as a whole to function to a higher degree.

In another preferred embodiment, keel 12 may utilize a split toe designwherein the split may be offset toward one side in order to allow acosmetic foot shell 14 with a separated big toe area in order to allowthe user to wear sandals. It is understood that keel 12 may not includeany split portions and generally remain with a full non-split keel 12.It is further understood that invention 10 may be adapted to utilize,retrofit, or integrate with existing known keels 12 in the prior art.

Curvature

In a preferred construction, curvature is contemplated at the end 48 oftoe portion 34 and/or at end 50 of heel portion 26 such that a naturalrollover during ambulation may be created and to provide keel 12 withcorrect positioning with respect to the ground to optimize energy returncharacteristics of keel 12. According to FIG. 23, the anterior andposterior ends of the foot shell may exhibit upward curvature to allowfor initial heel strike and terminal stance phase smooth transition, aswell as to decrease the load forces experienced between the foot shelland keel, to enhance durability. These curvature areas as well mayproduce enhanced roll over characteristics during ambulation.

At the anterior end of the keel, this curve up may be at or near theanatomical metatarsal head location. An additional curvature at thedistal end of the toe location may assist in smoothness of roll-over atterminal stance phase of the gait cycle. Still furthermore, in certainembodiments, the general anterior section of the toe may curl upward toallow for a forefoot rocker replication. This may functionally add toshorten the relative lever arm of the forefoot during late stance, butmaintain in providing necessary balance.

Still furthermore, as can be seen in FIG. 24, the keel may exhibituniform or non-uniform arch (es), and variance in the transverse planeat the first metatarsal head to better simulate the arches of theplantar-surface of the anatomical foot.

It is still further contemplated that forefoot or toe portion 34 may beslightly wider than the heel portion 26 to provide additional stabilityfor the user during later portions of stance phase of gait, as seen inFIG. 24.

It is understood that foot shell 14 should be able to accommodate abroader toe portion 34 such that a cosmetic appearance may still beachieved as well as more closely to approximate the shape of a naturalhuman foot. It is understood that other keel 12 shapes may beconsidered.

Considering many shoes have a built in arch support that often causes aprosthetic foot to tilt laterally in a shoe, it is contemplated thatarch 52 of keel 12 in the sagittal view will preferably be relativelyhigh as generally depicted in the drawings. In a preferred construction,a high arch 52 will allow an appropriately tailored foot shell 14 alsohaving a relatively high arch 54, to sit flat in shoes with high arches.Additionally, the curvature will provide smooth rollover characteristicsand provide the appropriate positioning of keel 12 with respect to theground for loading keel 12 to provide appropriate biomechanicalsimulation. Other heights of keel 12 arch 52 and foot shell 14 high arch54 may be considered.

Materials

In a preferred embodiment, keel 12 may be made from but is not limitedto carbon fiber and/or carbon fiber laminates, carbon laminatethermoplastics, thermoplastics, thermosets, or other. It is understoodthat other materials may be used that provide light weight, highstrength, high energy return spring characteristics, and may generallyhave relative simplicity of manufacturing. It is understood that carbonfiber usage allows for some energy return. Still furthermore, carbonfiber or other likewise materials may generally reduce the overallweight, which may be important to assist in decreased energy expenditurethrough limiting the inertial effects on the musculature of the residualleg.

Compliance

It is understood that keel 12 may generally consist of a thickness 56 toallow sufficient bending movement during stance phase of gait (heelstrike through toe off) yet will be sufficiently strong or stiff enoughto prevent breaking per the user's weight and activity level.Furthermore, unlike conventional prosthetic designs, the movement androll-over characteristics of the foot in this design are not dependenton the flexibility of the keel. Though the addition and flexibility ofthe keel do allow for increased energy return, slight accommodation ofuneven ground, and general compliance, they are not essential forperceived smoothness of gait in this design. Through the use of thecontrol system as described in greater detail below, this design mayallow for perceived smoothness of walking through controlled anklemovement versus simply keel compliance. This may greatly benefit thisdesign by allowing for the use of a stiffer, and therefore more durablekeel design, while maintaining the perceived smooth gait sense andnatural feeling ground accommodation. It is still further understoodthat in a preferred embodiment, keel 12 may be altered to accommodatethe resistant nature of bending during walking at different speeds, withvaried impacts, and for various terrains through various methods ofactuation or material characteristic alteration methods.

As will be discussed in greater detail below, a preferred constructionof keel 12 allows for more natural and intentional mimicking of NHL andmay provide the energy return at the appropriate time during the gaitcycle as with NHL, predominantly at or just before toe-off to simulategastrocnemious contraction.

In a preferred embodiment, middle portion 42 of keel 12 may have anon-uniform thickness to allow additional strength and durability forattachment to ankle joint assembly 16. It is also contemplated that keel12 may be flexible enough to have sufficient bending of keel 12 tocompensate for NHL shock absorption mechanisms which may have been lostdue to amputation such as the movement that can be found in thestructure of the human foot like the ligamentous and fibrous bands, aswell as with the compressibility of the meniscus pad found under thecalcaneus.

It is an object of this invention as well to at least partiallyreproduce the natural shock absorption through controlled plantarflexion after heel strike. Instead of solely relying on keelcompression, as conventional technology requires to produce shockabsorption during ambulation, the controlled ankle movement allows forsmoothness and shock absorption of gait. Thus, through keel complianceand/or control system accommodation, it is understood that suchconstruction may allow for a potentially smoother gait. Additionally,increased keel 12 flexibility may allow for better uneven groundaccommodation and enhanced energy return. The keel 12 thickness andcompressibility may also be tailored to the user's weight and activitylevel to provide optimum characteristics.

Keel Shape Fabrication

In another preferred and complimentary embodiment, the keel may bettermimic the natural stance phase of gait ground contact signature inshape. The keel may be fabricated from standard shapes or may be customfabricated for each user. In a preferred embodiment, conventional oralternative scanning or impression techniques may be used to fabricate abiomimetic natural stance phase of ground contact signature in shapeduring static, dynamic, or static and dynamic movement. The replicationof the natural ground contact signature shape is important not only forcosmetic symmetry, but also for natural roll-over characteristics andbalance. In a preferred embodiment, the user's sound foot, or if notavailable, a donor or standard system template foot, may be scanned forplantar surface signature during standing, walking, or other activitiesto provide information for keel shape and/or dynamic properties.Additionally, the scan may be used to capture the foot shape for thecosmetic covering. In a preferred method, the scan may be taken of theplantar and shape signature, imported into a computer or other digitalmethods, it may be manipulated in software to modify the shape,thickness, cutouts, or other qualities, then may be imported to afabrication device or method to output a physical keel. Throughmodifying the dimensions, thickness, rigidity, cutouts, ground contactsignature from standing or moving, and bracket/damper attachmentlocations, amongst others, the keel may be tailored to best match thedynamic qualities of the user's gait, as well as may help to optimizethe cosmetic appearance.

Attachment Location

The attachment location of the bracket or general damper assembly may bepositioned in relatively near proximity to the keel's posterior section.This may allow for a slight amount of keel compliance in this area, ormay allow for a fully stiff keel heel in this region. Additionalrigidity may be implemented through rigid keel components or bracketsystems implemented within the design. The use of a short keel leverposterior to the attachment point allows for the function of the heelrocker after heel strike of the prosthetic foot. This allows for betterbiomechanics replication of the natural foot post heel strike.Additionally, the keel may be integrated as one with the dampermechanism as well.

Still furthermore, it is understood that keel 12 may be integrallyformed with foot shell 14. It is further understood that invention 10may utilize an attachment means (not depicted) wherein invention 10 maybe attached to existing keel 12 designs available in the art.

Shock Absorption

As in the biomechanics found in natural gait, there is a minimalcompliance of the heel bony and ligamentous structure in this area. Themajority of the movement and shock absorption comes about throughmeniscus pad compression, controlled ankle plantarflexion, and fromother joints such as stance flexion of the knee, and minor hip movement,amongst others. The use of a semi-compliant foot shell, as well asengineered compliance between the foot shell and the keel, allows forreplication of the compliance naturally found in the heel bony andligamentous structures, as well as the slight shock absorption found inthe meniscus pad. The meniscus pad compliance may as well be replicatedthrough the keel compression in this area, but is more appropriately ismimicked by foot shell and foot shell/keel compliance.

Additionally, the arch of the foot may be higher on the medial side ofthe foot, medial longitudinal arch, than the lateral side, the laterallongitudinal arch, as can be observed as illustration in FIG. 23. Thiswould allow for a more natural positioning in the shoe, as well as formore of an anatomical replication of the stance phase ground contactsignature. Still furthermore, the keel may exhibit a slight transversearch in shape, similar to the anatomical foot structure. These threearches are important to allow for appropriate bio-symmetricalfunctioning of the plantar foot bony and ligamentous structure duringthe stance phase of gait and for shock absorption.

Ground Contact Compliance

Furthermore, the amount of relative distance from the transverse planecenterline of the keel distally may vary for various locations on thekeel. This may be in replication of the natural contouring of theanatomical foot. For instance, the area under the first metatarsal headmay be slightly lower to allow for increased ground contact force duringwalking in this area. This as well stands to enhance a natural groundcontact compliance and balance abilities. Other areas of the foot may becontoured with more or less curvature in these areas as well to providean increased or decreased ground contact force compliance.

Still furthermore, the keel may provide one, two, three, or four splitsin the anterior section to replicate the movement of the toes, andprovide increased compliance in those areas. These splits may run aportion of the length of the keel.

Still furthermore, the entire keel may exude, in certain embodiments,less compliant nature than conventional prosthetic foot keels. Inconventional designs, the keel is often made to be relatively flexibleso as to provide ground and ambulation compliance. This is largelynecessary due to there not being an ankle joint in the design, and theankle motion is exhibited through keel compliance solely. Since thepreferred embodiment exhibits a dynamic moveable ankle joint, andintelligent control thereof, the keel may be fabricated to be relativelystiff, and allow the vast majority of the compliance to come aboutthrough controlled ankle motion, and not through a highly compliantkeel. This is somewhat similar to that of the anatomical ankle joint,where the bony and ligamentous structure of the foot provides veryslight compliance, with more at the metatarsal-phalangial joints of thetoes, and the majority of the movement through ankle motion.

Rockers

During the stance phase of the gait cycle, the foot exhibits threerockers, or pivot points around which the body's mass rolls across arelatively fixed point to the ground. These three characteristicallydefined phases in the gait cycle are the heel rocker, ankle rocker, andforefoot rocker.

The heel rocker is exhibited from heel strike to foot flat portion ofthe gait cycle. As described in the previously filed application of thesame technology, this is controlled through eccentric, or lengthening,contraction of the anterior tibial muscles of the lower leg. Here, thecalcaneus is largely stationary compared to the ground, and the anklejoint rotates in the plantar direction, in a controlled manner. Asdiscussed in the preceding filed patent application, this is beingreplicated, in a preferred embodiment, through altering the state of thedamper system attached to the keel. After heel contact with the ground,the damper begins to change its state in a manner such as but notlimited to closing a valve in a hydraulic or MR fluid control device,increase current to a linear actuator, or other mechanically or fluidlyresistive devices. As the damper resistance increases, it slows theplantarflexion movement of the forefoot to make controlled contact withthe ground. This damper practically functions as the ankle jointequivalent. From the heel strike to the foot flat portions of the gaitcycle, the keel may provide slight or no compliance, but rather rely onactive ankle motion to provide this movement. As stated previously, in apreferred embodiment, the center of rotation of the ankle joint may bepositioned at or near the anatomical position, which allows for a shortlever arm from the posterior aspect of the heel to the center ofrotation, thus providing a plantarflexion moment after heel strike. Theamount of lever arm may be varied to provide a greater or lesser momentdepending on the desired effect. This may be modularly altered to allowfor variance. The movement of the damper during this portion of typicalgait cycles is providing a resistance to angular change, versusrequiring powered actuation. In certain instances during some gaitpatterns, active powered control may be necessary, as will be discussedin further detail below.

After the heel rocker occurs, the ankle rocker begins. This occurs afterfoot flat portion of the gait cycle. At this stage, there is a directionchange of the ankle motion from plantarflexion to dorsiflexiondirection. This information may be used, in a preferred embodiment toeffect the control system parameters, as will be discussed in greaterdetail below. From foot flat through later stages in the stance gaitcycle, the ankle motion provides resistance to change in thedorsiflexion direction. The amount of this change is relative to theamount of resistance in the damper mechanism, as well as the stiffnessof the keel. Regardless of the keel compliance abilities, the keel willprovide a loading response during these later portions of the gaitcycle, which may be unloaded in a spring-like manner at terminalstance—thus providing greater energy return, and less energy expenditureof the user.

The dorsiflexion resistance during this stage is increasing, in apreferred embodiment, to allow for optimal tibial progression,smoothness of stride, and stability. In a preferred embodiment, themedial and lateral longitudinal arches of the foot as well provide aloading response as the ankle joint becomes increasingly stiff duringlater portions of the stance gait. The particular shape—biomimetic inplantar surface contact signature, and contoured nature—provideincreased balance, spring return, and proper roll-over characteristics.

Additionally, the forefoot rocker may be further exhibited, in apreferred embodiment, through continued resistance in the final portionsof the stance gait cycle through allowing minimal to no movement of theankle joint, and relying on the roll-over characteristics of the keel.The leg (keel, ankle, and shin) rotates about the metatarsal head areasat this stage. The specific contouring, as discussed earlier, of theanterior keel, in a preferred embodiment, allows for increasedcompliance at or near the toe area of the keel to assist in thisforefoot rocker.

Keel Length

Additionally, in a preferred embodiment, the curvature of the anteriorportion of the keel may be such that it may curve upward toward the endto better mimic the natural toe movement. The toe area of the keel tofootshell connection, in a preferred embodiment, may be a relativelyloose positioning whereas to allow the anterior keel to migrate up anddown in the anterior portions of the keel so that a more cosmetic toemotion may be realized, without having to lessen the stiffness, andhence durability, of the anterior keel section. In an alternativeembodiment, the anterior keel may be affixedly or otherwise connected atthe anterior portion to the footshell. Additionally, the anterior end ofthe keel may be shortened compared to conventional keel lengths to allowfor the foot shell to bend in a realistic manner at the toes. This isonly possible due to the ankle joint allowing for varied resistanceduring the gait cycle. Because the ankle provides varied resistance, andhence varied angle for that resistance to occur at, the keel withrespect to the shin may be increasingly stiffened at a slightly moreplantarflexed angle compared to conventional systems, thereby allowingfor similar anterior support during the latter portions of the gaitcycle through maintaining a shortened keel length.

Still furthermore, alternative keel shapes, designs, contourings, andthe like may be implemented within this design to allow formicroprocessor, computer, or other control of an ankle joint to berealized in conjunction with a foot mechanism.

Still furthermore, the keel 12 may, in a preferred embodiment, mayextend to, or just past, the forefoot rocker location of the foot. Pastthe forefoot rocker area, a more flexible means may be utilized, such asthe foot shell, cosmesis, foam, or any other flexible type of materialto fill in the forefoot and toe areas. During the late portion ofterminal stance (at end of single limb support), the body weight rollsacross the forefoot rocker of the anatomical foot—near themetatarsophalangeal joint. During this portion of terminal stance, wherethe ankle torque amount is the greatest and this is where the greatestamount of pressure on the plantar surface of the foot is observed duringstance phase of the gait cycle. Anterior to this area, the toes providebalance, and minimal weight support. Therefore, by providing the keel toextend to just at or past the forefoot rocker area and providing aflexible anterior section, the biomechanics of the anatomical foot maybe further replicated and enhanced. Furthermore, the torque exhibited atthe ankle joint will be less than what is found in conventionalprosthetic feet, due to the terminal single limb stance pressure notextending as anteriorly. This will benefit this design by allowing forless torque to be found at the ankle joint, therefore increasingdurability. With conventional prosthetics feet, the keel extends to theanterior most aspect of the foot, while providing a spring returnthrough terminal stance from the keel bending. This causes there to bean excessive amount of torque at the ankle location, and on the keel.Because this innovation allows for a dynamic nature to the anklejoint—altering the angle of the ankle and angular resistance in realtime—the proper orientation of the ankle joint corresponding to thetransversed terrain can be optimized, and there is not the need for thefull length keel extension to the anterior most portion of the foot.

With conventional prosthetic feet, the angle of the ankle joint is notaltered during the stance phase of the gait cycle; therefore, thesupport of the body is dependent on the keel extending out to theanterior portion of the keel. Rather, what is found in the anatomicalfoot, is proper resistance at the time that the forefoot rocker is beingutilized, along with a proper ankle of the shin with respect to the foot(ankle angle), resulting in the ability to appropriately support thebody over the forefoot section without having to have a keel thatextends to the anterior most portion of the foot.

Still furthermore, the use of altering stiffnesses in the toe sectionthat extends out past the keel may be utilized to further enhance thesupport at this area. This may come about through state changingmaterials, actuators of various types, or other means to provide analtering to the toe stiffness or resistance to angular change, andhence, optimize balance. These may as well be utilized in conjunctionwith sensors, electronics, microprocessor, or other electronic means ofproviding intelligent control of the toes of the prosthetic device tooptimize energy return, and balance, among other qualities.

Foot Shell

In a preferred construction, foot shell 14 may be generally anatomicallycorrect and may further include a sufficiently high arch 54. This mayinclude a medial longitudinal arch, lateral longitudinal arch, and/ortransverse arch, or any combination thereof. The keel 12 foot may lock,snap, or form into the foot shell 14. It is understood that a SPECTRA,or functionally similar, sock may be used over foot keel 12 to reduce orprevent squeaking noises arising from the keel rubbing against the footshell 14. The same internal design of this said foot could be used witheither a left or right foot shell 14 for simplicity in manufacturing.

In a preferred embodiment, it may be desirable to provide a foot shell14 that is generally thin as to not limit the motion of the foot designthrough stiffness. It is contemplated that a thinner foot shell 14allows for full keel 12 dynamics although the invention 10 should notnecessarily be limited to such.

In a preferred construction, keel 12 is removably attached to foot shell14. It is contemplated that conventional means known in the art may beutilized. In a preferred construction, keel 12 may generally attach tofoot shell 14 by having a small protrusion extending out within theinside of the foot shell 14 in which keel 12 snaps in place underneath.

In an alternative embodiment, the keel may be integrally encapsulatedwithin a cosmetically molded foot shell, which may be customized to theindividual user. This method of fabrication may be similar to siliconrestoration, or other complimentary procedures to capture a biomimeticfoot shape. Still furthermore, in a preferred embodiment, the shape ofthe cosmetic covering may be replicated from the end user's sound limbvia scanning, impression, or similar shape and/or color matchingtechniques used in the field. Additionally, there may be amulti-durometer footshell utilized, in an alternative embodiment, whichmay allow for greater plantar-surface durability due to that area beinga high-stress area of the foot. Other areas may as well exhibit higherdurometers, such as but not limited to, the posterior heel, anterior,toes, top surface, or sides of the foot. The characteristics of ascanned image may be modified through a user interface system on acomputer or other electronics device, much like how the keel may bemodified through a user interface system. Various characteristics ofshape, coloring, durometer, size, weight, keel attachment location, andother characteristics defining the final cosmetic product may be alteredin the user interface and used to ultimately define the fabricationprocedure of the product. This image then may utilize a rapidprototyping method to form either a cosmetic cover or the mold to makethe cover.

Attachment Means

Invention 10 generally includes attachment means 24 to a user's lowerextremity (not depicted). Attachment means 24 may be but is not limitedto a male pyramid 58. It is understood that other conventionalattachment means 24 known in the art may be used such as but not limitedto threaded screws that matingly engage removable and non-removablebolts, removable pins, and so forth may be utilized. Furthermore, it isunderstood that male pyramid 58 may be of a female configuration and soforth.

Ankle Joint Assembly Inner and Outer Cylinder Relation

Referring once again to the drawings and in particular FIGS. 4, 4A, 4B,and 4C, ankle joint or joint assembly 16 generally comprises a housingor outer cylinder 60 that is generally connected to attachment means 24.In a preferred construction, outer cylinder 60 is generally in a fixedposition or non-rotational position relative to lower extremity andattachment means 24. Outer cylinder 60 generally includes an interiorcavity 62 and a center axis 64, which may or may not be located in thegeometric center of the unit. Furthermore, outer cylinder 60 may or maynot include first side cover 66, second side cover 68, and a range ofrotation restrictor mechanism 70. In a preferred construction innercylinder 80 generally attaches to keel 12 in a fixed or non-rotationalmanner such as but not limited to bracket assembly 20 which will bediscussed in greater detail below. It should be understood thatalternatively, outer cylinder may be in a fixed position relative tokeel. Conversely, inner cylinder would then be in a fixed positionrelative to attachment means and lower extremity. In the art ofprosthetics, it should be understood that having the outer cylinder forinstance being in a fixed position to the lower extremity or to the keelis one and the same and should not be considered limiting in any way.Each illustration is equivalent in nature to the scope of the invention.

Still furthermore, the prosthetic, orthotic, or robotic system is shownwith an energy transfer mechanism with variable resistance that canvariably restrict fluid flow through an orifice.

It is further contemplated that range of rotation restrictor bar 70 mayinclude cavity 72, which may generally be located along perimeter 74 ofouter cylinder 60 such that electromagnet 76, which will be discussed ingreater detail below, may also generally be installed in a relativelyfixed position relative to lower extremity and attachment means 24. In apreferred construction, outer cylinder 60 may be generally constructedof non-magnetic non-conductive material as will be described in greaterdetail below. In a preferred embodiment, electromagnet 76 is generallydisposed in cavity 72, which may also be generally disposed in range ofrotation restrictor bar 70.

Once again referring to the drawings and in particular FIGS. 5, 5A, 5B,5C, and 5D, generally disposed in outer cylinder 60 interior cavity 62is inner cylinder 80. It is understood that inner cylinder 80 generallyrotates around outer cylinder 60 axis 64, though axis may not be locatedat geometric center of unit. Furthermore, the term cylinder should notbe considered limiting, and is used for simplicity of explanation todescribe any arc-like movement path of the members, and may includenon-uniform or uniform arc paths.

It is further understood that inner cylinder and outer cylinder rotatein a relative motion with one another, and may or may not be in contactwith one another.

Shaft

Referring to FIGS. 6, 6A, and 6B, in a preferred construction, shaft 82generally is positioned and aligned along the interior cavity 62 ofouter cylinder 60 along axis or rotation 64 whereby inner cylinder 80 isgenerally attached to shaft 82. Whether shaft is at center of geometricunit or offset does not depart from the scope of the invention, as theaxis defines location of rotation of inner cylinder with respect toouter cylinder. Furthermore, shaft 82 generally aligns inner cylinder 80and outer cylinder 60. Shaft 82 is generally axially aligned andconnected by outer cylinder 60 first side cover 66 aperture 84 andsecond side cover 68 aperture 86. Shaft 82 may be made from non-magneticmaterial or magnetic material. Furthermore, at least one side cover maybe non-removably connected to outer cylinder.

Center Axis and Inner and Outer Cylinder Definition

The term “center axis” should not be considered limiting to define thegeometric center, while the term axis always describes the rotationalcenter of movement. Still furthermore, the center axis of the system mayreside outside any structural members. Still furthermore, the axis maygenerally describe the center of angular movement of the invention as awhole, and therefore may include any fluid filled, or other, assemblythat allows for altering a proximal and distal, inner and outer, orother orientation means of controlling dorsiflexion and plantarflexion.For instance, using a keel member with a more proximal strut orstructural member that rotate in relation to each other about a fixed ormoving rotational point, further constitutes two cylinders, or similar,rotating with respect to each other. While the described invention mayillustrate structural members in many of the figures, they are used forexplanatory purposes only, and should not be considered limiting in anyway. The relative rotary movement of these two members may constitute“inner and outer” cylinders, as the movement pathway of each membercreates a cylindrical or similar shape when moved through its arc. FIG.15 further depicts this equivalency. Still furthermore, FIGS. 45A and45B demonstrate the relationship between the inner and outer cylinder,axis of rotation, and other characteristics for the equivalency betweenvarious depictions of the two chamber damper mechanism.

Shaft may furthermore run along axis of both inner and outer cylinder,however, axis of the inner and outer cylinders may not run in thegeometric center of the damper unit, nor may the axis of the innercylinder be aligned with the axis of the outer cylinder. The innerand/or outer cylinders have an arc segment of a larger circle whereas aportion of the larger circle is not encompassed in the geometric damperarea. Additionally, the arc segment of inner and/or outer cylinder maybe of a CAM shape.

As discussed above, outer cylinder 60 may remain in a relatively fixedposition relative to lower extremity of user and generally secures shaft82 such that shaft 82 may rotate along axis 64. Inner cylinder 80 isgenerally attached to shaft 82 and rotates relative to user lowerextremity, or vice versa. In a preferred embodiment, shaft 82 is in arelatively fixed attachment to inner cylinder 80. It is understood thatother conventional rotational means may be provided wherein outercylinder 60 is in a relatively fixed position relative to user lowerextremity and inner cylinder 80 is generally free to rotate respectiveto user lower extremity.

Range of Motion

Inner cylinder 80 is generally constructed such that rotation alongcenter axis 64 is limited. In a preferred embodiment, inner cylinder 80includes top stop 88 (FIG. 7) which contacts outer cylinder 60 range ofrotation restrictor bar 70. Furthermore, inner cylinder 80 may includebottom stop 90 (FIG. 7) which contacts outer cylinder 60 range ofrotation restrictor bar 70.

It is understood that the range of motion limiting mechanism may bedepicted in numerous ways, all of which are considered one and the sameas the desires range of motion of the device is limited.

Referring generally to FIG. 7, it is understood that the human ankle hasa general range of rotation of about 15 degrees up (from horizontal 92)and a general range of rotation of about 45 degrees down (fromhorizontal 92). In a preferred embodiment, inner cylinder 80 isgenerally restricted from rotating up past 15 degrees by top stop 88contacting outer cylinder 60 range of rotation restrictor bar 70.Furthermore, inner cylinder 80 is generally restricted from rotatingdown past 45 degrees by bottom stop 90 contacting outer cylinder 60range of rotation restrictor bar 70. It is understood that the generalrange of rotation may be increased or decreased and the above exampleshould not be considered limiting. It is contemplated that greater rangeof motion or rotation may be desired for certain activities requiringmore general flexibility and, likewise, more restricted range of motionor rotation for other activities where less flexibility may be desired.

Cavity

The inner cylinder 80 may be made hollow or with lightweight core todecrease weight. It is understood that inner cylinder 80 may beweighted, filled with a deformable semi-solid material, fluid filled, orother such means where the center of gravity (not depicted) of the innercylinder 80 may move relative to the ankle joint assembly 16.

It is further contemplated that inner cylinder 80 may include a cavity78 for locating elements of the invention 10 and for possibly providinga water tight compartment for electronics, sensors, fluid controldevices and methods, or power source 130 used in association withinvention 10 which are discussed in more detail below.

It is contemplated that any combination of the above described designand orientation may be utilized without departing from the scope andfunction of the device. These above described orientations of thevarious sub-components should not be considered limiting in any way, asnumerous illustration are possible using inner and outer movingcomponents. It is understood for instance that the outer cylinder may beconnected to the keel, and rotate about the center shaft, which may beconnected to the lower extremity. In this preferred construction, theouter cylinder 60 is generally in a fixed position or non-rotationalposition relative to the keel.

Outer cylinder 60 stays in a relatively fixed position relative to keeland generally secures shaft 82 such that shaft 82 may rotate alongcenter axis 64. Inner cylinder 80 is generally attached to shaft 82 androtates relative to keel. In a preferred embodiment, shaft 82 is in arelatively fixed attachment to inner cylinder 80. It is understood thatother conventional rotational means may be provided wherein outercylinder 60 is in a relatively fixed position relative to keel and innercylinder 80 is generally free to rotate respective to keel. Innercylinder may then be attached to lower extremity via bracket or otherattachment systems.

Additionally, in a preferred embodiment, the center of rotation of theankle joint assembly should fall at or near the anatomical center ofrotation. It is understood that from user to user, the anatomical centerof ankle rotation may fall at slightly different locations with respectto the ground, proportions of leg segments, or other comparativemethods. It is therefore understood that the anatomical center ofrotation may not be exactly met through using this device, but that ingeneral the ankle joint falls in the anatomical center of rotationintended area whereas a natural looking ankle motion is apparent.

Additionally, it is understood that design may be fabricated usingvarious types of materials, including metals, allows, thermoformplastics, thermoset plastics, nanotechnology, carbon nanotubes, or anyother material known in the art.

Dampening System

Once again referring to the drawings and in particular FIGS. 8 and 8A,dampening means or system 18, generally refers to a means forcontrolling keel 12 rotation in association with and respective to theuser. Dampening system 18 may generally include electronic control,mechanical function, fluid dynamics, and combinations thereof. It isunderstood that invention 10 contemplates numerous means such ashydraulic, magnetic, mechanical or other constructions wherein thedampening, general control, or characteristics of the rotation of thejoint assembly 16 is achieved.

Magnetorheological Fluid General

In a preferred construction, magnetorheological or MR fluid or otherfluid types 94 is generally used for dampening the rotation of innercylinder 80 around the axis 64 of outer cylinder 60 whereby the fluid 94state of liquidity or viscosity is relatively controlled by selectivelycharging the MR fluid 94 via use of a permanent magnet or electromagnetor valving system 76. By example, where no or little dampening isdesired, the MR fluid 94 is not charged and generally stays in arelatively liquid state thereby creating little to no impediment forinner cylinder 80 from relatively freely rotating around center axis 64of outer cylinder 60. When dampening is desired, the MR fluid 94 isselectively charged to harden or somewhat solidify the MR fluid 94 sothat generally a viscous clutch, brake or impediment is created wherebythe rotation of inner cylinder 80 around center axis 64 of outercylinder 60 is slowed and/or halted.

It is also contemplated that MR fluid 94 may further act as a generallubricant for ankle joint assembly 16 outer cylinder 60 and innercylinder 80. It is still further contemplated that invention 10 may beutilized with hydraulic or other adjustable damper means to controlplantarflexion and dorsiflexion. It is understood that the currentinvention 10 may incorporate other means such as generally fluid typedampening other than MR fluid 94. Likewise it is understood thatinvention 10 may be carried out with no per se fluid and relay onmagnetic and/or mechanical dampening.

Surfaces and Construction of Magnetic Pathway

In a preferred embodiment, inner cylinder 80 further includes aconductive surface 96, which may integrally be part of inner cylinder 80or formed in as cover 98. Conductive surface 96 should generally be madefrom a material that is capable of carrying or conducting an electric ormagnetic charge and the term conductive should not necessarily beconsidered to be limiting. Conductive surface 96 may be made from metal,plastic with metal fibers, or other generally conductive materials orvariations thereof. Conductive surface 96 may include a first side 100and a second side 102 such that a generally larger surface area iscontemplated for interaction with MR fluid 94.

Furthermore, conductive surface 96 may be generally near or incommunication with shaft 82. Conductive surface 96 may include apertures104 and 106 for generally attaching with shaft 82. It is contemplatedthat shaft 82 may be of a conductive, metallic, or the like materialwhereby MR fluid 94 would also interact with shaft 82 in possiblerelative conjunction with conductive surface 96. Still furthermore,conductive surface 96 may have serrations 108, ridges or the like.

As discussed above, outer cylinder 60 is generally formed fromnon-magnetic or conductive material. In a preferred construction, outercylinder 60 includes conductive surface or strip 110, which may beintegrally formed with outer cylinder 60 or as separate element 112 asgenerally depicted. Furthermore, conductive surface or strip 110 mayhave serrations 114, ridges or the like (FIG. 4A). In general, outercylinder 60 strip 110 is aligned with inner cylinder 80 conductivesurface 96. In a preferred construction, strip 110 may further include afirst side 117 and a second side 119, which may generally interact withinner cylinder 80 conductive surface 96 first side 100 and second side102, respectively. Still furthermore, strip 110 may generally connect orbe in contact with shaft 82. Conductive strip 110 may include apertures116 and 118 for generally attaching with shaft 82.

The inner cylinder 80 conductive surface 96 and outer cylinder 60conductive strip 110 may include serrations 114, ridges or the like in agenerally radial direction from center axis 64 in order to increase orhelp MR fluid 94 lock down in the presence of an electric or magneticfield and thereby increases direct shear mode response. It is furthercontemplated that such construction would additionally increase thesurface area for MR fluid 94 communications and interaction.

It is contemplated that void, space, or cavity 120 is generally createdbetween outer cylinder 60 and inner cylinder 80 and generally filledwith MR fluid 94. In a preferred embodiment, inner cylinder 80 isgenerally disposed in outer cylinder 60 such that a general closeproximity may be achieved to limit the amount of MR fluid 94 needed withpossible exception to areas specifically where the given distance wouldbe optimized for fluid dynamic characteristics. Furthermore, MR fluid 94may act as a general lubricant to decrease friction between the innercylinder 80 and outer cylinder 60 during rotation. It is alsocontemplated that having the inner cylinder 80 and outer cylinder 60 ina relative close proximity would increase or benefit the structurallateral torque stability of the dampening system 18.

It is still also contemplated that shaft 82 may be made of conductive ormagnetic properties in order to assist or decrease or prevent possibleleakage of the MR fluid 94. By example, such construction may generallymake the MR fluid 94 generally more viscous and not as likely to leakthrough holes or potential holes in seals.

Now referring to FIG. 9, in a preferred construction, electromagnet 76is generally in communication or contact with outer cylinder 60conductive strip 110, which is in communication with or contact with MRfluid 94, which in turn is in communication or contact with conductivesurface 96 of inner cylinder 80, thereby forming electric or magneticflux circuit 122. This may be illustrated in any number of ways to forma magnetic pathway.

Spacers 124 and 126 made from but not limited to nylon may also beutilized in a preferred construction and generally be placed betweeninner cylinder 80 and conductive strip 110 to decrease or preventcompletion of circuit 122 aside from charging the MR fluid 94 incompletion of circuit 122.

Power Source

Power source 130 is generally in contact or communication withelectromagnet 76 via wires 128. It is contemplated that the dampeningsystem 18 may have a low draw of energy consumption, and thus a smallbattery 132 may be utilized. In a preferred construction, battery 132would preferably be lithium ion in nature but is not limited to such.Power source 130 can be placed anywhere on the prosthesis for ease ofreplacement and may include an attachment port (not depicted) forrecharging. Additionally, for optimizing the weight distribution, powersource 130 can be placed externally such as on the socket or pylon. Itis also contemplated that the power source 130 could selectively beplaced higher, keeping a higher center of gravity for minimizinginertial forces during running. As discussed above, power source 130 maygenerally be located in cavity 78 of inner cylinder 80 or shaft orpylon. Additionally, battery may be charged using plug in style,inductive style, or other rechargeable battery methods.

Lock Out Safety Feature

Furthermore, electromagnet 76 may also incorporate a safety features toallow a manual lock such as but not limited to a permanent magnet forthe event of power loss. It is contemplated that as a potential safetybackup, wherein by example a power source 130 level were to decrease toa certain level, a reverse polarity may be created to cause thepermanent magnet to slide into position to lock joint assembly 16 ordampening system 18 or means may also be used to de-gouse the MR fluid.By example, a permanent magnet may be slid into a desired position(manually or electronically) to create a positive lock at a fixed angleto allow the user to ambulate with some or all of the motion coming fromthe keel 12 compression such as may be found in prior art standardprosthetic feet. Once recharging or power source 130 returns to arelative normal condition, the polarity would again reverse back to itsnormal state, causing the permanent magnet to move out of position, andinvention 10 may then operate via the electromagnet 76. As power levelsbecome low, an indicator, such as audible or vibratory alert may beused. Still furthermore, manual of electronic means of largely lockingout the ankle joint may be implemented in various methods and forms withany type of mechanical, fluidly, or otherwise controlled dampermechanism.

Fluid Restriction System

It is further contemplated that joint assembly 16 and dampening system18 may include a magnetorheological or other dampening which may operateby either or both direct shear and pressure driven mode to generallyincrease the resistance ability of the joint assembly 16. As statedabove, dampening system 18 may of numerous construction contemplatedwithin the scope of invention 10.

Referring to the drawings and FIG. 9A in particular, it is still furthercontemplated that a mechanical based servo or permanent magnet system133 may be used in conjunction with or as opposed to electromagnet 76.It is further contemplated that tapered magnetic and nonmagnetic pieceswhich are joined together with which the permanent magnet slidesagainst, valve movement via a servo or motor, or other methods in orderto vary the magnetic field interacting with conductive piece number 110,or adjust fluid flow characteristics in general. In a preferredconstruction, fluid restriction system 133 may include a small servo ormotor mechanism 135, such as but not limited to one utilizing gears, toslide back and forth.

In general, the means for controlling fluid flow cumulatively may beconsidered one and the same, and generally can collectively be referredto as fluid restriction system.

Additionally, mechanical based servo/permanent magnet system 133 mayinclude a hydraulic adjustable valve (not depicted) to control theamount of fluid passing between outer cylinder 60 and inner cylinder 80.The valve may be controlled as well by a small servo or motor mechanismor other actuation methods. It is understood that all known or novelactuation methods would provide equivalent function and purpose andmethod of actuation of fluid restriction device should not be consideredlimiting in any way. It is contemplated that electro-mechanical basedservo system may require less energy consumption and may therefore bebeneficial in certain applications.

Dorsiflexion Assist

Dampening system 18 may also generally include spring system,dorsiflexion means or dorsiflexion spring system 137. It is contemplatedthat dorsiflexion spring system 137 may cause the ankle joint assembly16 to dorsiflex during swing phase of gait. Dorsiflexion spring system137 may comprise a spring of conventional nature, hydraulic piston,combinations of both or other conventional spring biased devices orother actuation strategies known in the art including but not limited toactive and passive power actuations strategies. The term dorsiflexionspring should not be considered limiting, but rather, should generallydescribe means of assisting to raise the foot into dorsiflexion throughone of several means during the initiation of the swing phase of gait.Dorsiflexion spring system 137 may be attached or located anteriorly orposteriorly to the dampening system 18 or ankle joint assembly 16(compression or extension spring, depending on the location forshortening or lengthening, respectively). Still furthermore, in apreferred embodiment, active powered control of the dorsiflexion mayoccur through hydraulic or other fluidly controlled means, mechanicalmotorized, linear actuator, or other means. In general, the use ofdorsiflexion in a computer or electronically controlled ankle joint canbe characterized by one of several means. As will be discussed below,the method and approach in general of initiating dorsiflexion during theappropriate moment in the gait cycle is an important element of thedisclosed invention. Utilizing dorsiflexion in a passive (spring-likesystem) or active (powered hydraulic, electrical, or other) manner, asdescribed in this invention, and the preceding patent, are uniqueelements of this disclosure. After the toe-off portion of the gaitcycle, providing active dorsiflexion enables the user to gain adecreased change and occurrence of stubbing the toe or stumbling duringthe swing phase of gait. Further details of the method of initiatingswing phase dorsiflexion will be discussed below.

The spring load resistance may be changed through adjusting the springdrive length, changing to a lighter or heavier spring, or adjustingspring placement. Additionally, it may be altered through electronicmeans such as but not limited to user interface systems, allowing thepractitioner in the field, or patient to adjust the springcharacteristics, dynamic movement characteristics including but notlimited to angular change, timing, angular velocity, angularacceleration, force, and range of motion, or through embedded controlusing sensors, microprocessor, or the like. Still furthermore, thedorsiflexion mechanism may be initiated via sensor, mechanical, orsoftware based systems, as will be discussed in further detail below.Still furthermore, information such as angular change, angular velocity,force during the gait cycle, ground contact information, or otherbiomechanics sensor related information may be used to initiate andcontrol the rate of angular change over time, as well as the amount ofangular change of dorsiflexion during the swing phase of gait.

Additionally, the dorsiflexion spring may only come into effect uponcompletion of specific parameters, such as but not limited to after toeoff has occurred. For instance, if the user is going to sit down andprop their feet up, they may purposely not initiate a true gait cycleand hence not perform a true toe off, and therefore not allow theprosthesis to go into dorsiflexion so that it does not provide anuncosmetic effect during their activity. It should be understood thatthe above example is used for illustrative purposes only and that thereare numerous defining methods of preventing the initiation of toe off,each of which may be customized to the particular user.

Compliant Hydraulic Mechanical System

Alternatively, the control of the ankle joint may come about throughaltering the state of the keel to shank sections through compliant fluiddynamic means. As opposed to conventional hydraulic or other fluidlyactuated means, the use of compliant hydraulics allows for the actualhousing compartments for the fluid be compliant in nature, therebyallowing for natural give to occur while managing forces and movement.

In a preferred embodiment, one or more fluid filled damping systems maybe utilized to prevent motion in the plantar and dorsiflexiondirections, or other movements for other joints. In order to moreclearly explain the workings of such a system, a description of twofluid filled dampers will be explained in order to provide a simplicityin explanation, but should not be considered limiting in any way. Insuch a system, these compliant fluid filled hydraulic dampers may befabricated with compliancy to their movement, or may be moreconventional damper methods as are used in the hydraulic industry.

With using a compliant natured device, the fluid filled damper may befabricated out of rubber, plastic, laminate, or other flexible orsemi-flexible (compliant) material selection. The damper compartment mayhave one or more grooves or contouring built into it in order to assistin the flexibility or compression of it. Additionally, it may havevolumetric limiting agents associated with its design to limit theamount of expandability it has in certain directions. Still furthermore,these fluid filled compartments may be fabricated so that compression ofthe system may occur in one direction only, or in more than onedirection to provide additional compliancy. These fluid filledcompartments may be attached to the keel, the keel and the outer strutsor structural members, just the outer struts or structural members, orneither. In general, the compression of the outer struts or members inrelation to the keel may cause pressure on the fluid filled compartment,and may force fluid to travel from one compartment to the other througha fluid line. As this fluid may be constricted in its ability to travelfrom one compartment to the other, such as would occur in closing thevalve system, the compressed strut in general may become increasinglytougher to bend, and therefore provide a more rigid, less compliantsystem, though the compliant nature of the fluid cavities may provide asmooth transition of the movement and forces. In essence, as the valvecloses, the fluid is unable to travel from the compressed fluid filledcompartment to the other, the strut is therefore not able to be pushedcloser to the keel, and in general, the ankle joint is not moved. It isfurther contemplated that a conventional hydraulic system may encompassan embedded compliant member in order to provide equivalent benefit.

In a preferred embodiment, the fluid filled compartments may be attachedto both the keel and the associated strut or member, although is notnecessarily limited to such and may be attached to one or the other, orneither. By doing this however, while the posterior strut for instanceis being compressed and moving closer to the keel during fluidexpulsion, the anterior fluid compartment may be filling with fluid,forcing the anterior strut away from the keel. By attaching the fluidcompartment with the keel and strut, it may prevent excessive movementof the strut from the keel—in essence, holding the strut to the keelthrough vacuum-like force within the fluid filled compartment duringbiomechanically attempted extraction of the system.

The fluid filled compartments may be located within an enclosed unit, orwithin an open unit, all together being equivalent in nature to a rotaryunit as a whole with inner and outer cylinders. FIGS. 15A and 15Billustrate some specific embodiments. In FIG. 15A, a two chamber rotaryunit is depicted with an inner and outer cylinder, which moved about anaxis of rotation. Furthermore, the two chambers 501 and 502 are fluidfilled compartments, and valve system restricts fluid flow from onechamber to another. The FIG. 15A embodiment comprises a two chamberdesign with an inner and outer cylinder and an axis of rotation usingsealed fluid compartments to maintain the fluid within the space betweenthe structural members. FIG. 15B depicts the same two chamber designusing an inner and outer cylinder, and an axis of rotation of the two.FIG. 15B uses enclosed fluid compartments to maintain fluid within theappropriate space.

It is still further contemplated that various chamber elements may havedifferent functions, including but not limited to power generation,power storage, energy storage, spring-like mechanisms, or other methodsdiscussed in this disclosure.

Still furthermore, the system may use spring loaded wiper seals or otherseals commonly used in the sealing industry. Additionally, it may useclose tolerances to achieve sealing.

The compartments may be sealed using flexible material with an openingorifice for connecting to a valve system, and may reside within theenclosed structural members, or may reside outside or among thestructural members. In either case, the fluid movement is controlled byvariable fluid pressure within the fluid compartments by means of valvesopening and closing, and not solely by means of variable fluidviscosity. It is understood in addition that through using MR fluid,inherently, the fluid is controlled via variable fluid viscosity.

While the above mentioned illustrations may appear slightly different inpractice, the function, means of actuation, strategy, overall design,and other aspects are equivalent in nature, and should not in any way beconsidered limited to such expressions. Many equivalent means ofdepicting such a concept are contemplated, including but not limited tochanging from a two chamber design, to a one, three, four, or othernumber of chambers, which remain in equivalency to a two chamber designin function and performance.

Through using compliant members, a more natural movement and feel willoccur in the system. Still furthermore, the sealed compartments withinstructural members, and through using seals such as but not limited toO-rings, are by nature compliant compartments, in that the overall shapeof the compartments may change shape as the system goes through a rangeof motion. Additionally, using fluidly controlled systems as well havecompliance as the fluid may compress, the structural members may flex,and the valves may have a transition of restriction gradient as it mayclose or open.

The use of a valve in the fluid line may allow the fluid flow to berestricted in either, or one, direction. The use of electronic means toadjust the fluid flow may allow integration of the control system tosuch a mechanical and fluid dynamic system.

Still furthermore, the use of no electronic means may allow for a userselectable alteration in heel and toe load compression of the footadjustments. Still furthermore, with a mechanical type of system,separate settings may be used for dorsiflexion and plantarflexionsettings.

Strut or Structural Members for One Embodiment

The struts or structural members (term used interchangeably) may befabricated out of flexible or non flexible members. There may oneanterior and one posterior struts, or there may be more than oneanterior and more than one posterior struts in order to provideadditional inversion/eversion compliancy. The struts, in general, in apreferred embodiment, may be concave in nature, meaning, curved inwardtoward the center of rotation of the system. It should be understoodhowever, that the struts may be generally straight or curved out aswell, and not depart from the overall function of the system. By havingthem curve inward, a better cosmetic appearance will occur. These strutsmay run, in a preferred embodiment, from the attachment point of thefoot to the shin, to the keel. The posterior strut may generally attachto the posterior aspect of the proximal keel. The anterior strut maygenerally attach to proximal keel anterior to the center or rotation.The length of keel, which the anterior strut attaches to, may beadjustable to the particular user, or may be set in a fixed location.These struts may exhibit compliancy to assist in plantarflexion anddorsiflexion of the system, or may be fabricated with more rigidity andrely on flexible members within the struts to provide bending, such asbut not limited to a hinge or hinges.

Still furthermore, the keel in such a system, may have generalcompliancy built in, or may have little to no compliancy. Because thesimulated ankle joint has so much inherent compliant nature to it, theremay not be a need to rely on compliancy from the keel, as is found inconventional systems.

The use of fluid, such as but not limited to water, oil, solution, air,or other fluids may be used to provide the damping method of the fluidfilled compartments. Altering the fluid flow of any one, or all, of thecompartments may in general affect the observed stiffness of the strutsand keel during ambulation or other activities. With the valve systemfully open, the system may in general have a relatively loose feel,while when the valve system in fully closed, the system may exhibit arelatively stiff feel.

Axis of Rotation and Center of Rotation

The center of rotation, or equivalently an axis of rotation of thesystem may occur outside the actual mechanical components, in freespace, or within the boundaries of the mechanisms. It is understood thatthe net effect of an axis of rotation outside of or at a non-geometriccenter of a mechanical device ultimately results in the equivalency of acenter of rotation of the movement, as the term center by definition isthe point at which the rotation is centered. Having the axis of rotationoffset from the mechanical geometric center still allows for themechanical components to rotate and have a center of rotationequivalent.

FIG. 16 depicts a center of rotation offset from the mechanicalstructure geometric center, and depicts an outer cylinder with acomparable axis of rotation. This design should be considered inequivalency to other depicted two chamber systems. Still furthermore,FIG. 17 demonstrates an axis of rotation, and hence range of motioncenter of rotation, outside the structural member center of mass. Stillfurthermore, means of inducing a moving axis of rotation, or movingcenter of rotation may be implemented in equivalency.

Other Methods of Implementation

FIGS. 19 and 20 depict variations in the size and shape of the inner andouter cylinders, and hence the fluid compartments. Each of these, aswell as other illustrations depicted, should be considered one and thesame in equivalency, and should not be considered limiting in any way.

Still furthermore, it is contemplated to use a linear damper method tocreate the equivalency of an inner and outer arcs of rotation about anaxis point. This method of implementation may encompass other attributesshown in FIGS. 21A-C, though not to be considered as limiting to such.As illustrated therein, a linear damper 600 is disposed so as to controlthe rotation of the foot, through a range of motion.

Still furthermore, the use of rotary to linear motion may beaccomplished according to FIGS. 22 and 23. In a preferred embodiment,the two chambers may be located side by side, though are not limited tosuch methods.

Still furthermore, the use of hinged segments may be used to compresscompliant fluid compartments or actuators, which may allow for movementof the device. Still furthermore, this design encompasses the same innerand outer rotatory cylinders, axis of rotation, and two fluid chambers.The method of compressing the fluid compartments may be by compliant ornon-compliant members to force fluid from one compartment to another.These illustrations are used for explanatory purposes only and shouldnot be considered as limiting in any way.

Sealing

In a preferred embodiment, the damper may use fluid of various types tocontrol movement, as fluid may flow from one chamber to another. Thefluid may be restricted through a valve type of system known in the art.Furthermore, seals of any nature may be used to prevent fluid flow fromone chamber to another. The seals may be single, double, or other innumber, and may be made of various materials known in the sealingindustry, and may be fabricated specially for static of dynamic nature.Additionally, the fluid compartments may be fabricated out of fluidsacks, or the like, which may reside within structural members, or mayreside amongst structural members. Whether the fluid is held withincompartments by standard or custom seals, or within sealed sacks, thefunction is equivalent in nature. The term sacks is not meant to beconsidered limiting, but rather is used for explanatory purposes only,and is to include other forms of containing fluid, such as but notlimited to seals, chambers, balloons, structural members, compliantcontainers, and the like. Still furthermore, the fluid sacks may befabricated out of any compliant material, and may encompass a means forattaching the fluid sack to valve system(s). The use of fluid filledsacks, as opposed to using standard seals, may further assist indurability of the device. The compliant nature of the fluidcompartments, or sacks, is to allow for the fluid to be moved from onechamber to another. Whether residing within structural members, oramongst structural members, the fluid flow characteristics is the same,and the fluid compartment must account for fluid moving from onecompartment to another, and therefore must change shape. It should beunderstood as well that the term compliant may encompass thecharacteristics of expandability, or may not be expandable, but onlycompressible in nature.

Bracket Assembly

Referring to the drawings and in particular FIGS. 10 and 10A, in apreferred embodiment, bracket assembly 20 would generally comprise amedial bracket 134 having aperture 136 and lateral bracket 138 havingaperture 140 wherein aperture 136 and aperture 140 are generally axiallyaligned and receive shaft 82. Furthermore, medial bracket 134 aperture136 and lateral bracket 138 aperture 140 may be generally in a circularshape 142 with a flat portion 144 for matingly engaging shaft 82circular portion 146 and flat portion 148 (FIG. 6B).

In a preferred construction bracket assembly 20 is pivotally connectedto outer cylinder 60 such that the rotational movement is along centeror rotation axis 64. It is understood that other attachment means may becontemplated wherein bracket assembly 20 is connected to inner cylinder80 in a generally fixed manner and yet in a pivotally rotational mannerwith outer cylinder 60. It is contemplated that bracket assembly 20 isattached to keel 12 by attachment means 150 such as but not limited toscrews 152, 154, 156, and 158. Other conventional attachment means 150may be used wherein keel 12 may be easily and quickly be removed forother configurations of keel 12.

It should be further understood that connecting outer cylinder to thekeel, and providing brackets to attach shaft to lower leg section of theprosthesis characterize the equivalent function of the system, andshould not be considered limiting or altering from the previous patentapplication disclosure. This synonymous method may lend to providingincreased durability of the system. Again, conventional attachment meansmay be implemented to attach bracket assembly, outer cylinder, and othersuch components of the system. In either case, the brackets are utilizedto provide a connection between the components, such as but not limitedto the keel, damper, pylon, fluid compartments, struts, etc. Thebrackets are designed such that they do not impede the range of motionof the damper.

It is further understood that bracket assembly 20 may be of a singlepiece construction (not depicted) wherein medial bracket 134 and lateralbracket 138 are joined in the middle on the distal aspect to possiblyprovide additional stability. The contouring of the brackets assembly 20is preferred to minimize weight and optimize strength. In a preferredconstruction, apertures 160, 162, 164 and 166 are formed to reduce thematerial used in generally forming bracket assembly 20.

In a preferred construction, bracket assembly 20 is made from materialthat is light weight and provides minimal torque movement. Materials maybe but are not limited to composites, plastic, laminated material,aluminum, titanium, or other metals. It is understood that alterationsto the shown design of the bracket assembly 20 may be contemplated toprovide other configurations for optimal strength and minimal weight.

Washer (not depicted) may be used between the outer cylinder 60 andbracket assembly 20 to generally decrease friction. Washer may berecessed into the brackets and/or outer cylinder to allow more precisionfit of components against each other.

Joint Assembly Placement

Again referring to the drawings and in particular FIGS. 11, 11A, and11B, in a preferred construction, the placement of the joint assembly 16will be such that center axis 64 of rotation will generally fall throughan anatomical weight line region 168. It is understood that typicallyaccording to the anatomical chart, weight line region 168 isapproximately 28.2% of the foot length anterior to the posterior aspectof the skeletal structure of the foot. It is contemplated that jointassembly 16 rotation along center axis 64 rotation is generally along ananatomical center of rotation 170 of a natural ankle joint. It isunderstood that this position is in relatively close proximity to theposterior aspect of the foot, and as such the bracket assembly 20 forjoint assembly 16 may begin just posterior to the weight line region 168and run forward for support. It is further contemplated that positioningof the joint assembly 16 will provide additional keel 12 heel portion 26compression abilities and uneven ground accommodation.

Still furthermore, the bracket or outer cylinder may attach at or nearthe posterior aspect of the foot, lending to little to no compression ofthe keel at that region. Additionally, the center of rotation of thedamper may fall further posterior, anterior, distal to, or proximal tothe anatomical center of rotation. It is understood that providing ajoint center of rotation near the anatomical center of rotation may havesignificance in replicating the biomimetic nature of the design,however, through design constraints, optimization of system performance,and other reasons, there may be benefit to alter the location of thejoint center of rotation. For instance, placing the damper center ofrotation further anterior to the anatomical position may assist inproviding a longer lever arm to increase plantarflexion moment afterheel strike. Still furthermore, this may as well lend to functionallyshortening the toe load lever arm and hence minimize the joint torquesexperienced during later portions of the stance phase gait cycle.

It should also be noted that while the keel 12 heel portion 26 mayprovide some compressibility from heel strike to foot flat, the majorityof the plantarflexion action will come about through true plantarflexionof the keel 12 through the damper in order to better mimic NHL andprovide for optimal push off characteristics at toe off, which isdiscussed below.

Furthermore, an inversion/eversion damper system (not depicted) may beutilized at the base of the dampening system 18 to further accommodateuneven ground. This may include bumper systems, compressible materialssuch as urethane or the like, joint systems, and the like. Also, otherconventional inversion/eversion systems or methods may be implementedinto this design to further provide uneven ground accommodation.

Finally, the use of electronically characterized means may beimplemented to provide inversion and/or eversion characteristics. To dothis, the use of additional damper systems, actuators, hydraulics, MRfluid, motors, springs, gears, sensors, microprocessor, or other meansmay be used to control the movement.

Feed Back Sensor System

Referring to the drawings again and in particular FIG. 12, in apreferred embodiment, invention 10 may utilize a feedback sensor system22. It is contemplated that feedback sensor system 22 will provide thedampening system 18 either directly or indirectly information such asbut not limited to weight distribution on keel 12, forces generated onkeel 12, impact times on portion of keel 12 and so forth fordetermination of user gait cycle to automatically control joint assembly16 operations. Sensor system 22 may also include a strain sensor, momentsensor, pressure sensor, gyro sensor, accelerometer, or the like thatmay communicate with microprocessor unit 172 via wires 186 orwirelessly, as well as power source 130. Furthermore, feedback controlsystem 22 may include a time sensor or real time clock and angle sensor,of various kinds, to compare angular velocity and acceleration (linearand/or angular) relative to center axis 64 of dampening system 18 tofurther assist in control of joint operations.

It is contemplated that invention 10 may further but not necessarilyinclude a microprocessor unit 172, or other electronic systems, whichcommunicates with sensor system 22 and in turn generally controls orcommunicates with the dampening system 18 of joint assembly 16 whichwill be discussed in greater detail below. It is understood that theterm, feedback sensor system, should not be considered limiting.

It is contemplated feedback sensor system 22 may be generally located onkeel 12, damper, bracket assembly, within damper or bracket assembly, onor in pylon system, or other locations. It is still further contemplatedthat feedback sensor system 22 may include heel sensor system 174generally located on or in relation to heel portion 26 and toe sensorsystem 176 generally located on or in relation to toe portion 34, oralternatively located on or within brackets or damper to provideequivalency of information of toe and heel pressure, contact, movement,force, and other sensor related information.

Furthermore mechanical or liquid pressure/force sensors may be includedwithin or part of dampening system 18 to determine force generally onheel portion 26 and/or toe portion 34. It is understood that other typesof known sensors in the prior art may be used such as sensors thatmeasures microscopic bending of the titanium tubular pylon to determinepressure on heel and forefoot, and others.

In a preferred construction, heel sensor system 174 may further includesensor 178 and 180, on heel portion 26 medial segment 30 and likewise onheel portion 26 lateral segment 32 respectively. Furthermore, toe sensorsystem 176 may further include sensor 182 and 184 on toe portion 34medial segment 38 and likewise on toe portion 34 lateral segment 40,respectively. It is contemplated that more sensors may be utilized andlocated around other portions of keel 12, brackets, or damper joint toprovide additional information to further enhance the control of thesystem as a whole. Other types of information such as but not limited togravity, linear accelerations, rotational accelerations, sound,vibration, temperature, may be provided through other types of sensors,to again, further enhance the function and control of the system. In apreferred construction sensors and sensor systems communicate withdampening system 18 and/or microprocessor 172 via wires 186 or wirelessmeans (not depicted in figure). It is understood that the term dampingsystem should not be considered limiting, and encompasses all methods ofaltering movement of the keel with respect to the limb, and may includeboth resistive and powered actuation methods.

It is contemplated as well that the addition of more than oneaccelerometer may be used in combination to detect movement in variousdirections, such as but not limited to inertial elements of gait,notably foot position with respect to the ground such as but not limitedto incline and decline. Accelerometers may as well be used inconjunction with gyros to combine movements of more than one jointsimultaneously and in general to coordinate movement, orientation ofmovement, and other characteristics during usage of the device(s).

Microprocessor Real-Time Feedback

It is contemplated that microprocessor unit 172 will give real time gaitanalysis throughout the gait cycle as well as control the MR fluid 94liquidity, solidification, or viscosity, or equivalently, providecontrol of other types of damping systems such as but not limited tohydraulic, compliant fluid systems, electronic or other valves, etc. Itis contemplated that microprocessor unit 172 may function as the“prosthetic brain”, but should not be considered limited to such. Thisdesign may incorporate, but not be limited to, time sensors or real timeclock 188, angular sensor 190, heel portion 26 load, force, strain, ormoment sensor or sensors 192, and toe portion 34 load, force, strain, ormoment sensor or sensors 194. It is also contemplated that momentsensors or strain gauges may be utilized.

Time sensors or real time clock 188 may be utilized to regulate eventssuch as allowing invention 10 to lose all, or much of the plantarflexionresistance when the user is sitting, thus, allowing the foot to be at anatural angle which is discussed in greater detail below. Stillfurthermore, force, angle, moment, and other sensors may be used toprovide information to control plantarflexion resistance during sitting.

Furthermore, time clock 188 could regulate aspects of gait based on aprofile of optimal timing for the user. Timing, as meant here, refers toproviding appropriate angle, resistance to angular change, and dynamicbiomimetic movement throughout the gait cycle, and in normal dailyactivities—providing movement that replicates the timing of the naturallimb for those various functions. The timing of the joint's movement maybe a function of its resistance and angular change over time. It isfurther contemplated that some of the discussed functions may notnecessarily only be based on time factors, but may also be based onmovement, such as but not limited to angular change, rotary accelerationchanges, linear acceleration changes, location reference changes, orother information, or time and movement input to microprocessor.

Still furthermore, the term microprocessor should not be consideredlimiting, and may encompass other types of electronics, software,computer technology, nanotechnology computing, reconfigurable computing,and other systems, all of which should be considered as one and thesame.

Angle Sensor

In a preferred construction, angular sensor 190 may be incorporatedwithin the inner cylinder 80 and/or outer cylinder 60 or its equivalentto determine the relative angle of the keel 12 to user lower extremity.Angle sensor 190 may be fixed in the joint assembly 16 to determine thedegree of rotation between inner cylinder 80 and outer cylinder 60. Itis further contemplated that a level device (not depicted), such as anaccelerometer, may be used to generally determine the keel 12 anglerelative to ground.

Control of Gait

It is still further contemplated that microprocessor unit 172 could beprogrammed to control speed and amount of plantarflexion at keel 12 heelportion 26 striking of the ground also referred to as heel strike. It isalso contemplated to utilize existing prior art such as OTTO BOCK C-LEGfor control mechanisms, through combining function of the this foot andankle system to conventionally available prosthetic knees. In anotherpreferred embodiment, invention 10 may work in conjunction with anartificial knee wherein microprocessor unit 172 could be utilized forboth joint functions, as will be discussed in further detail below.Furthermore, it is contemplated dynamic factors could be programmed todenote how “hard” a patient generally walks. The general amount (angleand force) of plantarflexion used in walking may be set to determinepush off characteristics. For example, the speed and amount ofdorsiflexion of the foot after toe off may be set. Each of thesecharacteristics may be set for normal walking as well as adapt to changeas the user gait changes. The sensory feedback systems 22 may cause themicroprocessor unit 172 to change the damper characteristics as speedincreases or decreases, or when walking on non-level terrain. Eachaspect of ankle and foot gait characteristics may be modified through inorder to appropriately tailor the user's gait for perfect symmetry,safety, and function of all activities.

Programming

In a preferred embodiment, microprocessor unit 172 may be programmedwith various memories or programs 196, include communication electronics198 for interfacing or programming, and provide audible signals 200 orvibratory signals for warnings of malfunction, power level, etc.

Location

Microprocessor unit 172 could be located just anterior to the anklejoint assembly 16 on top of keel 12 or may be located on the inside ofthe inner cylinder 80, within pylon, or other locations as generallydiscussed above. It is further contemplated that microprocessor unit 172may be located on a lower extremity prosthesis wherein a user is missingpossibly above knee or below knee but above ankle.

Power Source

As generally discussed above, power source 130 is contemplated forelectric supply for dampening system 18. It is further contemplated thatpower source 130 may be located in or integrally formed withmicroprocessor unit 172 and provide power for microprocessor unit 172.Power source may as well be located on any location in or aroundprosthesis including in or on prosthetic pylon, within foot shell,within cosmesis, or other locations. In a preferred construction, wires173 may connect microprocessor 172 to power source 130.

It is still further contemplated that microprocessor unit 172 mayinclude a current supply and power or battery management system 202 forfurther optimizing power consumption. System 202 may include on and offtimers for powering down while the invention is at rest for periods oftime. Typically, unless the user is sleeping or doing other non-movingactivities, there will be some change in angle or force at any giventime frame when the user is supporting weight, however it is known that“rest” periods of time may be for more or less than one secondintervals, on regular or non-regular interval time basis. It iscontemplated that invention 10 may include an automatic system (notdepicted) such that if no force change is detected on sensor system 22,during a designated time, invention 10 may power down to conserveenergy. In a preferred embodiment, invention 10 would power downautomatically when not being worn by the user whereby the user would nothave to manually turn invention 10 off. System may as well automaticallyturn back on when user intends to use the prosthesis. This may beaccomplished through means such as but not limited to on switch,accelerometer sensor, movement sensor, system angle sensor, forcedetection sensor, or other means.

Still furthermore, the user may be able to check the battery level witha handheld electronics device, computer interface, initiating specificsensor readings on the device (for instance, but not limited to: tappingthe foot in a particular manner, or other such activity that mayinitiate specific sensor response sequence), or other methods, which mayprovide audible, visual, vibratory, or other signals to portray batterylevel, or other such information.

Power Generation

It is also still further contemplated that power source 130 may be of aregenerating nature wherein the power source 130 is re-supplied throughmechanical means such as but not limited to a Faraday type device.Furthermore, known technology for self-winding mechanisms with rotors,as found in self-winding or self-powering watches may be utilized. Stillfurthermore, fluid power or mechanical power generation methods may beimplemented. It is understood that through the course of normal dailyactivities of using lower extremity limbs, there is a considerableamount of force used to prevent movement of the joints within the limb.Through a prosthetic device, this movement may be limited throughdamping mechanisms. The resistive force that is used to prevent themotion of the joint angle, may as well be used to store energy(mechanical or electrical) to power the device. This may as well comeabout through a system such as hydraulic reservoir or other suchmechanical or fluidly controlled means, but not limited to such.Additionally, electrical power generators may be implemented to provideadditional power for the system, including all or some power requiredfor operation.

Wire/Wireless Connection

In a preferred embodiment, microprocessor unit 172 may be wirelesslyprogrammed or controlled such as through wireless technology. It iscontemplated that a user could wirelessly regulate, command, or programspecific functional parameters on demand such as modifying the dampeningsystem 18 incrementally and selectively through a remote control.Likewise, invention 10 may include a hardwired controller (not shown)generally mounted in a relatively accessible manner on the invention 10.

Connection with Other Components

As will be discussed in greater detail below, microprocessor 172 may beused in conjunction with a myoelectric sensor system 400 and/or asensory feedback or proprioception system 300. In a preferredconstruction, microprocessor 172 may be utilized as the primary and onlyelectronic control and processing device for invention 10. It isunderstood, however, that multiple units may be used that work inconjunction or separately to perform the various tasks. Stillfurthermore, one central microprocessor may encompass various controlprograms, functions, such as but not limited to proprioception, sensoryfeedback, myoelectric, functional level alterations, and others, whichmay be accessed through the user or practitioner opening the option foruse of that particular control program, given the systems application. Agiven device, ankle, knee, hip, or other, or any combination thereof,may have one microprocessor, or its equivalent, which may encompassvarious forms or illustrations of control programs, which may beselected from to match up with the needs and desires of a particularuser. Still furthermore, a knee or hip design for instance may use themicroprocessor from the ankle, which may have embedded or associatedcontrol program(s) for the more proximal joints.

Proprioception/Sensory Feedback Stimulator

Referring again to the drawings and in particular FIG. 12A, in apreferred construction of invention 10, prosthetic proprioception system300 may be included. The term proprioception generally refers to generalcommunication from the prosthesis to the user, including but not limitedto angle, force, resistance to angular change, temp, and other feedbackmodalities. Still furthermore, proprioception system inherently includesinformation from sensors to the microprocessor, or its equivalent, tocontrol movement. In either case, information from the extremity isrelayed to the control mechanism, whether human or prosthetic brain, toinitiate a response in intended movement alteration and knowledge.

The more feedback information that the prosthesis can provide to theuser, the greater the external physiological proprioception may be. Withconventional prosthetics, the ability to understand externalphysiological proprioception is relatively simple because theprosthetics movement is consistent. With a device that has the abilityto change its state—angle, resistance to angular change, etc.—the needfor greater feedback is essential because the user has no other way ofknowing the prosthetics state, and the external physiologicalproprioceptive sense may be inherently limited. According to FIG. 33,the prosthetic, orthotic, or robotic system as a whole may function in asimilar manner as to the anatomical sensory feedback mechanisms, whichinclude input from the user, actuation control of angle, angular change,resistance to angular change, force, and other parameters, and thenrelays information from the extremity back to the user, brain,controller, microprocessor, or their equivalent.

It is contemplated that the invention 10 may provide instantaneouscommunication or signals from the prosthesis to the user whereinfeedback is provided such that a sense of spatial and/or angularorientation of a prosthetic joint is achieved, as well as otherproprioceptive information such as resistance to angular change.

For reference, FIG. 12C generally illustrates elements of a naturalhuman system for proprioception feedback pathway. Furthermore, FIG. 12Dgeneral illustrates a flow chart depicting elements of a natural humansystem for proprioception feedback.

It is understood that in the human body, the brain analyzes the requiredmovements of our extremities as well as has knowledge of the positioningand resistance to change of our joints and orientation in space. Smallproprioceptor sensors in the human muscles and joints, such as jointkinesthetic receptors, neuromuscular spindles, and neurotendinousreceptors, send sensory information to the brain to tell it where thelimb is orientated in space as well as its movements such as stretchingof the muscles or bending of the joints.

PRIOR ART

It is also understood that there are systems in the prior art whichrelate to pressure sensor on the prosthetic foot or hand which may relayinformation through a small microprocessor and then stimulate the limbin a similar fashion, thus tricking the brain in thinking that thewearer is “feeling” with the prosthetic limb. It is contemplated thatinvention 10 may provide information relating to the angular positionand change, including resistance to angular change, within theprosthetic joint and stimulate the limb 308 in a designated manner, thusproviding what may become a subconscious feedback of the position andangle of the limb's spatial orientation. Furthermore, the resistance tothat angular change may be characterized through proprioceptivefeedback.

Safety and Energy Expenditure

It is contemplated that invention 10 may provide greater safety through“knowing” the position of the prosthetic joint in space, as well as theresistance to that change. By example, “knowing” or “feeling” that theankle joint is plantar flexing excessively due to wearer beginning towalk down a hill. This information may be especially important to theuser due to the dynamic state of the ankle joint. Conventionalprosthetics move in a fixed resistance about a fixed point, thereforeproviding movement that is expected by the user.

Furthermore, it is also contemplated that there will be a decreasedenergy expenditure through providing a more natural gait pattern as wellas providing an enhanced mental confidence in the prosthesis andtherefore greater functionality. Likewise, the user may have a sensethat the prosthesis is more of a part of them through enhancedhuman/machine interaction.

It is contemplated that the user's brain will learn the sensory feedbackfrom the system as subconscious proprioception or cerebral projections.While numerous methods of stimulus may be incorporated, some may providemore information that the user can comprehend.

It is contemplated that the user would generally connect, communicateand interact with joint assembly 16 via communication means or system302. It is further contemplated that a separate microprocessor 304 maybe utilized or microprocessor 172 or even a combination thereof. It isfurther understood that prosthetic proprioception system 300 may beutilized on other joints as well as ankle joints or other prostheticjoints, such as knee, hip, hand, elbow, and shoulder.

Furthermore, it is contemplated that the prosthetic proprioceptionsystem 300 may be utilized on an individual that has lost feeling orlost the sense of proprioception or control in their natural extremity.

The use of Sensory Feedback in prosthetics may assist the user in havinggreater safety, symmetry, and lifelike appearance in ambulating, as wellas provide enhanced psychological connectivity between the prosthesisand the user.

Proprioceptive, and other Sensory Feedback information, may be used tofurther assist the microprocessor to function in the most appropriatemanner possible, through providing additional information to the controlprogram. Still furthermore, when considering that in a preferredembodiment, the prosthetic system as a whole should interact, connect,and communicate with the human body as one complete system. In doing so,with the user being able to “feel” and in general comprehend thehappenings and environment conditions of the prosthetic system, the usermay be able to further control the function, movement, and actions ofthe prosthetic system.

Types of Feedback

In a preferred construction, it is contemplated that feedback mechanisms306 may include pressure variance with angular change or resistance toangular change, pressure movement with angular change or resistance toangular change, electrical impulse to limb 308 with angular change orresistance to angular change, vibratory variance with angular change orresistance to angular change, and other conventionally known methods.Furthermore, it is contemplated that prosthetic proprioception system300 may utilize angle or positional sensor in conjunction or separatelywith a sensor to detect resistance to angular change of a prostheticjoint, and provide feedback thereof. It is further understood thatalterations of the sensor signal of any of the above mentioned or othermethods, of stimulation may occur to characterize more than one type ofsignal through a given mode of stimulation. For illustration purposes,altering amplitude and frequency of an electrical stimulus may provideat least two distinct pieces of information, relating to angular changeand resistance to angular change. Other methods of altering signals maybe used in equivalency to provide necessary or desired information tothe user.

Now referring to FIG. 12E, generally illustrated is a flow chartdepicting a preferred embodiment of invention 10. It is contemplatedthat integration of the various sensors and feedback may be controlledby microprocessor 172 or through an independent processing system orcombination thereof.

It should be further understood that other sensory stimuli systems maybe implemented in a similar manner, such as but not limited to force,vibration, tactile stimulation, direction of force, texture, shape,audible, and other stimuli—all defined by the term Sensory Feedback. Theterm Sensory Feedback should not be considered limiting, but should ingeneral define providing information to the user of the actions,movements, sensor information, and other desired information that may begained from the prosthesis to the user.

Connectivity

Referring now to FIG. 12F another preferred construction is generallydepicted wherein keel 12, dampening system 18, ankle joint assembly 16,sensor system 22 is in general communication with wires 310, or throughwireless means, through microprocessor 312, power source 314, sensorystimuli contact 316 and wires 318. It is understood that microprocessor312 may be microprocessor 172 or through an independent processingsystem or combination thereof. Power source 130 may also be used. Sensorsystem 22 may include angle or position sensor 320, force sensor todetermine resistance to angular change, or others. Likewise, FIG. 12G isa general flow chart of a preferred embodiment invention 10 asdiscussed.

Now referring to FIG. 12H, another preferred embodiment of invention 10is generally depicted wherein the prosthetic is directed to a non-anklejoint although a prosthetic hand is generally illustrated, it isunderstood that invention 10 may be utilized on other joints,prosthesis, orthotics and combination thereof. Socket 322, frame 324,sensory stimuli contact 326, wires 328, cosmetic cover hand shell 330,internal hand components 332, hand motor 334, hand connector piece 336,power source 338, microprocessor 340, angle/position sensor 342 andother force and other sensors, and hand connection piece 344 aregenerally shown working in communication. Likewise it is understood thatpower source 338 may be utilized separately or in conjunction with powersource 130 and may also be but is not limited to a myoelectric or otherbattery. It is also understood that microprocessor 340 may bemicroprocessor 172 or through an independent processing system orcombination thereof.

The stimulatory feedback devices may be incorporated within the socketsystem to interact with the residual limb, outside of the socket system,mounted on or in the prosthetic frame or socket, mounted within a cuffor other embodiment for use as a housing, or other means.

Myoelectric Sensor System

Once again referring to the drawings and in particular FIG. 12B, apreferred construction of invention 10 may further include a myoelectricsensor system 400 wherein a generally closed loop sensory feedbacksystem is contemplated. Myoelectric controls and/or myoelectric sensorsystem 400 may provide a prosthetic system wherein instantaneouscommunication or signals from the user to the prosthesis is achieved forbetter regulating, controlling, or positioning the prosthesis. It isunderstood that the human body produces electrical signal throughmuscular and other activity.

It is understood that the term myoelectric may generally refer tocommunication from the user to the prosthesis, and may includeconventional technology to read nerve signals through surface orimplanted means, or other methods such as but not limited to patternrecognition. Other methods of reading communication from the user to theprosthesis are actively being developed, including but not limited toimplanted peripheral or cortical nerve sensors, which may be used tocontrol such a device. Still furthermore, information from the soundlimb may be used to control the movements of or inputs to the device.This may be done during a training session, or may be done for typicaluse.

This control program, in a preferred embodiment, may utilize signalanalysis, signal decoding, pattern recognition, neural control, or othermethods of processing the myoelectic signals to effect the damper. Themyoelectic signals as well may come about through surface, implanted, orother methods of characterizing myoelectric signals from the body. Itshould be understood as well that other methods of taking informationfrom the human brain or efferent nervous system, and applying that tocontrol prosthetic movement may be utilized as well, such as but notlimited to implanted electrode arrays, nerve grafting with electronicselements, or other means. In general, any method of controlling aprosthetic device through intended human initiation, conscious orsubconscious may be utilized.

The control program may allow for myoelectric, neural integration,pattern recognition, or other such human to prosthesis, orthotic, orrobotic interface to have an alterable effect on the control. Forinstance, the neural integration strategy may provide up to 100% controlof the devices movements, or may provide 0% of the movements. The amountor percentage of the influence that such devices may have can beadjusted manually through any available means including but not limitedto the GUI, or may be automatically altered through control programparameters, such as but not limited to be correlated with the user'savailable strength, abilities, functional abilities, neural sensorsignals, sensor signals, or may be altered gradually over time, as wellas other methods. By altering the effect that the neural integrationstrategy may have over device control may be advantageous duringtraining of the user for the device. This may allow someone with poorneural integration control of the device to gain greater functioningslowly over time as the system may force the user to have increasingcontrol of their neural signals.

Still furthermore, the prosthesis system may employ pattern recognitionto differentiate between different user inputs or to analyze thehistorical data stored in its memory bank to recognize different gait orterrain patterns. This functionality may be present initially, or may bea feature, which is unlocked at a later time, or may be installedseparately as an update. This is only meant to be an example, and thepresence or absence of this feature is not meant to be limiting in anyway.

The prosthesis system may use learning algorithms for patternrecognition such as Hierarchical Temporal Memory algorithms or any otheralgorithms applicable to that purpose.

Virtual Reality Training

Still furthermore, the user may place any of the available neural inputstrategies on the sound limb in a manner as to extract necessary data,integrate a virtual reality, or its equivalent, system to control thefunctions of the prosthesis. This may include, but is not limited topattern recognition, myoelectric input, accelerometers, and other suchsensor data. Still furthermore, the use of data and neural inputcapturing devices may be used on other parts of the body not includingthe extremities, including but not limited to the brain. It is furthercontemplated that the user may move his/her sound limb in a manner in orout of the virtual reality system that is typical for a given activity,and the neural information may be processed to ultimately control theprosthetic device in a similar manner. The user may use imagery as wellto gain symmetrical neural inputs to both sides, of which may beprocessed to better control the limb. This may be done as well toincorporate pattern recognition systems into control of the device.

Control of Gait

It is contemplated that in a preferred construction, dampening system 18is generally controlled by the myoelectric sensor system 400. It isunderstood that myoelectric sensor system 400 may or may not necessarilycause movement of the ankle joint assembly 16, but rather is allowingthe user to adjust the rotation or slow down the angle progressionduring stance or swing phase of gait. The joint assembly 16 movement maystill generally be achieved through natural biomechanical movementduring ambulation besides or in addition to the inclusion ofmyoelectrics. The dampening system 18, corresponding sensor system 22such as pressure, and myoelectric sensors system 400 generally may limitthe speed or movement, such as angle change, of the ankle joint assembly16 as it rotates. It is contemplated, therefore, anatomical musculaturecontrol of the lower extremity prosthesis, or more specifically theankle joint assembly 16, is achieved. It should be understood that theterm damping system should not be considered limiting, and shouldinclude any such method of articulating, moving, changing the state of,expanding, contracting, bending, or any other means of adjusting themechanical assembly to initiate and cause joint movement or simulatedjoint movement.

It is further understood that myoelectric sensor system 400 may beutilized on other joints as well as ankle joints or other prostheticjoints, such as knee, hip, hand, elbow, and shoulder, as well asorthotics. Likewise, it is understood that myoelectric sensor system 400and proprioception system 300 may be both included in a preferredembodiment or separately. It is understood that some myoelectric systemsare known for use in upper extremity prosthetics and knee systems.

Myoelectric sensor system 400 may include stimulators or controls 402which may be placed on the residual limb 404 of a user (i.e., on thepretibial and gastrocnemious group for transtibial amputees) or otherareas outside of the prosthesis, to control or manage dampening system18. By example, as the user fires their gastrocnemious muscle group,such as they naturally would during the midstance to toe off portion ofthe gait cycle at the beginning of midstance, invention 10 may increaseresistance in the dampening system 18 and therefore provides greaterresistance toward toe off portion of the gait cycle. User may thenactively control their joint angle during ambulation as with a realfoot.

Powered and Resistive Control

Furthermore, it is contemplated that damper may be dynamically oractively controlled, passively controlled, or a combination of dynamicand passive control through myoelectric or user input. Dynamic controlrefers generally to providing active power to initiate and change, atleast partially, the speed, angle, or resistance to angular change ofthe damper. This method may provide all or partial, augmented power, tothe damper to assist control. Passive control generally refers to theability to altering the resistive nature of the damper only—wherebypreventing angular change, and hence effecting speed of the damperduring gait. A combination of both active and passive power may utilizetimes of damper control using a resistive nature and active powerednature during various times of the gait cycle. This may be beneficialthrough mimicking the eccentric and concentric contractions of the legduring walking.

For instance, the user may want to provide 100% power to the user, sothat the device lifts them up a flight of stairs with little to no powergeneration of their own. Conversely, the user may want to provide 70% ofpower (or 70% of body weight) so that they have to provide the resulting30% with their thigh or other muscles. This would enable for an“augmented power” system and force the user to use his own muscles toprovide movement, resulting in improved musculature, circulation, andproprioceptive control. Furthermore, the control system could be set toprovide less and less power over time so that the user slowingstrengthens his muscles by forcing him to perform the same action withless power from the device. This would be beneficial duringrehabilitation.

During the gait cycle, the anatomical leg may eccentrically contract toresist angular change, such as between heel strike and foot flat, whenthe tibialis anterior muscle eccentrically contracts to slow theplantarflexion of the foot. Alternatively, the anatomical leg mayconcentrically contract during the gait cycle, such as after toe offwhen the tibialis anterior muscles cause the foot to dorsiflex duringthe swing phase of gait for instance. It is understood that acombination of active and passive power may be beneficial in a preferredembodiment to best simulate full gait biomechanics and dynamicproperties. Still furthermore, it is understood that the utilization ofactive, passive, or a combination of active and passive control may beutilized to characterize ambulation. The use of myoelectics to controlsuch movements may be used in combination with a control program to bestcharacterize intended movement. Still furthermore, the user of a sensoryfeedback or proprioception system may be used to characterize themovements from the prosthesis to the user.

Augmented Power

Still furthermore, augmented power may generally be realized throughproviding partial dynamic or active power of the device for the intendedmovement. It is contemplated that it may be beneficial to provide aportion of the power necessary for intended movement of the prosthesis,and rely on the user to provide the additional power. For instance, whentransversing up a flight of stairs, it is contemplated that providing aportion of the power to raise the user up each step may come aboutthrough initiation of dynamic, active power of the knee, and rely on theremainder of the power necessary to raise the user up the step from theuser themselves. This may be beneficial by allowing the user to maintainthe need for utilization of their own musculature to maintain strength,coordination, and provide inherent proprioception of their intendedmovements through the prosthetic device. The level of augmentation ofthe power of the prosthesis may be controlled through a control program,which may be set by a practitioner or user, and may be manually orelectronically altered over a period of time for training and userability purposes. The amount of power that the prosthesis provides,versus the user, may be varied over time, in correlation to the user'smyoelectric signals, in correlation to the user's muscle strength,through use, or other systematic alterations. In addition, the level ofpower that the prosthesis may provide may decrease a certain amount overtime so that it systematically causes the user to rely more and more ontheir own muscle strength. This may be a beneficial therapy tool.

Benefits

It is contemplated that a preferred construction may enhance muscle toneand muscle strength in residual limb 404 and consequently may improvecirculation. Of note, 70% of amputations are secondary to circulatoryinsufficiencies. Invention 10 may therefore prevent higher levelamputations as is often the case with patients with severe circulatoryinsufficiencies.

Accordingly, invention 10 may also provide control for the user,increases safety, symmetry, confidence during ambulation, and furthercontrols plantar-flexion and dorsi-flexion. Likewise, it is contemplatedenergy or power required myoelectric sensor system 400 and/orproprioception system 300 would be minimal relative to other powergenerally contemplated by invention 10.

Functions/Ambulation

Generally referring to the drawings and in particular FIGS. 13, 14, 14A,and 14B, the following changes to the invention 10 in general ordampening system 18 in specific may be allowed to best mimic naturalhuman locomotion during ambulation. It is understood that the controlprogram and its associated functions, characteristics, methods,methodologies, implementation, and the like, may be equivalentlyutilized in other joints such as knee, and hip, for prosthetic,orthotic, and robotic applications. Still furthermore, the controlprogram uses means of taking any number of sensor signals thatcharacterize limb motion and may process the sensor signals, along withtime signals, and may use that information, amongst others, tocharacterize limb defining moments, and may hence compare to typicallimb motions during ambulation and non-ambulation activities. It isunderstood that the DOUBLE HUMP GRAPH as depicted in the original patentapplication is characterized by these characteristics, as the generalpatterns of the graph demonstrate a change in resistance levelsassociated with defined moments in the gait cycle, which must becomprehended or understood or defined by the sensor's data.

Furthermore, as described in the original patent application, the doublehump graph illustrates the general resistance, and hence relativeinverse relationship to angular velocity, of the ankle angle during thegait cycle.

In a preferred embodiment, the plantarflexion angle may be increasedduring the gait cycle corresponding to increase in speed.

Control System Calculation Strategies

The control system in general may operate through any number ofmathematical models, artificial intelligence programs, equations, neuralnetworks, or other methods of controlling such a device, and should notbe considered limiting. In one embodiment, the system's control may bebased off of approximating nonlinear functions using methods such asneural networks to provide feedback controllers for systems where theweights of the neural network are updated based on the critic function.In a preferred embodiment, defining points may be used with equations asstated below to control such a system, but should not be consideredlimiting in any way.

Ambulation and Defining Points

It is understood that during the walking gait cycle, there are definingpoints, which illustrate the normal locomotion parameters. Thesedefining points generally include Heel Strike, Foot Flat, Midstance,Heel Off, and Toe Off. It is understood that between Heel Strike and ToeOff the limb is generally in a Stance Phase of gait. It is alsounderstood that between Toe Off and Heel Strike, the limb is generallyin a Swing Phase of gait. It is known that, in general, these describeddefining points fall in progression, but that it is also sometimesobserved that these defining points may occur in various other ordersthrough various abnormal or other gait activities. These defining pointsmay be used in the below descriptions for illustrative purposes, andshould not be considered limiting in any way. They are meant for clarityof reading and comprehending the complicated functions of the controlprogram. Furthermore, it should be understood that other gait dynamiccharacteristics occur, such as but not limited to ankle rocker, heelrocker, forefoot rocker, and others. These various biomechanicsparameters of the gait cycle should be largely replicated through thefunctions of the control program in general.

Types of Actuations Strategies

It is understood that invention 10 may include various forms ofactuation, such as but not limited to hydraulic, mesofluidics,pneumatic, regenerative, MR fluid, active or dynamically powered,passively powered, mechanical, or other methods, including but notlimited to Newtonian and non-Newtonian based fluids. The describedcontrol program for invention 10 should not be considered limiting whendescribing a particular means of activation or actuation, but rather, itshould be understood that the described methods in general depict acontemplated form of actuation in conjunction with the control program.Other expressions of actuation strategies may be implemented inconjunction with the described control program, and do not depart fromthe scope and purpose of the described invention. The control programmay be modular to work in conjunction with various expressions ofactuation strategies.

Still furthermore, the system may provide spring-type, elastic-type,resistive-type, and/or powered-type actuation, or any combination of theabove during the gait cycle. This may be accomplished through alteringthe state of various, or numerous, valves or their equivalent, tocontrol the fluid flow between various chambers in order to allow thefluid to travel from one method of actuation area to another within thesystem. Still furthermore, other components may be added to allow, forinstance, the hydraulic fluid to fill a spring loaded, or otherresistive methods, compartment during high pressure within the system.This would allow for storage of energy during the portions of the gaitcycle where there is excessive energy being dissipated, and stored forrelease at the appropriate biomechanical time when active muscular pushoff occurs for instance, such as but not limited to stair descent or atthe end of the stance phase of gait. Still furthermore, it may be usedfor joint positioning. This may allow device to exhibit variablestiffness, spring, active power, and/or resistive motions depending onthe valve and fluid flow path.

Valve Position and Resistance Correlation

Again, the description of valve position manipulation may as well becorrelated to other actuation expressions such as through mechanical orother means. The description of valve position manipulation is meant fordescriptive purposes, and should not be considered limiting. It isgenerally understood that in reference to a hydraulically, pneumatic,fluidly, or MR fluid actuated system (or other types of systemsincluding a control valve), the valve position may be correlated withresistance. As the valve may tend to close, there may be a larger forcerequired to initiate or sustain movement in the damper. Conversely, as avalve position may tend to open, allowing more fluid to pass through,there may a lower amount of force to cause or sustain movement in thedamper. Likewise, the resistance of the damping unit is generallyinversely proportional to angular velocity, ω, during normal ambulatoryactivities. As the valve may tend to be in a more closed position, theunit may tend to move through a given angle more slowly, given a force,and therefore angular velocity may be lower. It is important tounderstand this general relationship in order to understand the generalpremise of the control program.

In a preferred embodiment, the valve position is being controlled. It isunderstood that equivalently, the resistance, angle, angular velocity,angular acceleration, or other parameters may be controlled bycontrolling the valve. Because each of these variables is highlyrelated, for explanatory purposes, the discussion will refer in generalto controlling valve position only. It is understood that the term valveposition may be equally replaced with other variables, and methods ofimplementation, and not depart from the scope or intention of theexplanation. The particular explanation is suited for readability andcomprehension, and should not be in any way considered limiting. It isunderstood that many other equivalent methods of altering the state ofsuch a damper mechanism may be expressed, resulting in similar effect,and does not depart from the scope of this disclosure. The term valveshould not be considered limiting in any way.

Valve Types

It is contemplated that any number of valves may be used that reside inthe prior art, to control such a device. In general, invention usesvariable fluid flow characteristics of the valve system to managemovement of the device. This includes variable orifice size orcontouring, or its equivalent, variable flow types through the orifice,and altering the thickness of a variable fluid within a valve, amongstothers. These may include but are not limited to needle valves, rotaryvalves, servo valves, electronic valves, pressure valves, check valve,gate valve or any other type of valve that may be used in a hydraulic,fluidly actuated, pneumatically actuated, mesofluidic, or other system.Furthermore, these valves may be controlled by pulse width modulation orother known methods. One depiction of a preferred embodiment, though notlimited to such, may be a valve similar to FIGS. 26 and 27, where anon-uniform, slanted, arched, screwed, or other groove, hole, opening,contouring, or other may be used to provide varied resistance of fluidpassing through or by.

Valve Signal Strategies

Still furthermore, the valve system may be controlled using pulse widthmodulation, as depicted in FIG. 32. Other methods of implementation maybe used as well including but not limited to direct movement control,pulse code modulation, bi-phasic chopper drive controller, or othertypes of chopper drive controllers, current control, voltage control,modulated control, and others.

Compliance Control

It is further understood that mechanical and fluidly controlled systemsoften inherently have compliance and lag time associated with theirfunctions. An associated control program may therefore account for suchlag time or compliance in order to best suit the functions of mimickinggait biomechanics. This lag time enables for the processor toinstantaneously make alterations to the end valve position, intendingfor a new fixed position of the valve, and rely on the slowness of sucha valve to make it to that new valve position to provide a smoothtransition of movement as the anatomical body would as well, forinstance, have a gradual change in its state of resistance within ajoint. It is understood though, that with faster mechanical or fluidlycontrolled systems with little to no lag time, the control program ingeneral may provide a gradient to the valve position in order to“smooth” out the motion of the unit. It should as well be understoodthat the term valve should not be considered limiting but is used ingeneral for explanatory purposes for those skilled in the art ofrobotics and prosthetics.

Calibration

It should be further understood that invention 10 may not require manualcalibration of device for some sensor data. Instead, as the ankle joint,or other given joints associated with control program, goes through agiven range of motion, the control program may set the maximum andminimum angles as end range points. If during ambulation, a greater orlesser angle is reached passed what may have already been established asan end range, the new value may take its place, establishing a new endrange. Equivalently, other sensors, such as but not limited to forcesensors, may provide their own input to the control program,microprocessor, or other, to set or initiate end range values.

Embedded Sensors

Because the use of numerous sensors in such a system may add cost andcomplexity, and lower durability and dependability, it is generallydesired to use fewer sensors to control such a system, while maintainingconsistency in control. In a preferred embodiment, the described controlsystem may limit the associated control system sensors to an anglesensor, and force sensor, along with charting time with a real-timeclock or alternatively similar device. It is understood that alternativesensors may be used, added, replaced with, or altered to provide similaroutcomes, including but not limited to nanotechnology sensors, includingcarbon nanotubes, to determine force, force transition, temperature,pressure, vibration, or other information. In general, it is understoodthat sensors in general provide information to the microprocessor orother computer system to provide a “reaction” and affect the damper in agiven way. Many various types or combinations of sensors may be used toprovide similar outcomes. The described methods should not be consideredlimiting. Other types of sensors that may be utilized may include, butnot be limited to, acceleration, gravity, magnetic, global positioningsystem technology in general, or others to provide a similar outcome asthe described control program.

The described method of attaining appropriate information for thecontrol program is through taking angle information to extrapolateangle, angular velocity, and angular acceleration information.Furthermore, a force sensor is used to determine if there is weightbeing applied to the foot, and in particular to the forefoot and/or heelregions. It is not necessary to have a highly calibrated force sensor,but rather to assess if there is weight being applied or not, especiallyat the forefoot region. This enables the sensor system to be more robustand less dependent on variations in sensor reading. It is furtherunderstood, however, that the precise information pertaining to theforce data may be further assessed in biomechanics analysis, which willbe further discussed below. Additionally, highly calibrated force datamay be used to further accentuate the functions of the control program,or may be used to provide information to other joints, such as the kneeor hip. Additionally, the use of multi-strain-gauge sensors may be usedto provide force data in various planes to better control movement ofthe prosthetic, orthotic, or robotic system—which may include ankle,ankle and knee, ankle knee and hip, or other combinations thereof.

Still furthermore, force and/or torque data may be extrapolated fromangle, angular velocity, or angular acceleration data, in possibleconjunction with valve position data through mathematical equations.Because the control program sets valve position, it therefore hasknowledge of valve orientation according to encoder or other sensor orelectronics methods. Additionally, with known angle, and hence angularvelocity and acceleration data, in conjunction with valve position data,other information such as force and torque data may be extrapolatedthrough mathematical equations. There is a mathematical correlationbetween valve position, angular velocity/acceleration, angle, and othersuch parameters.

Furthermore, it should be understood that highly calibrated sensors maybe used to assist the functions of the control program, but as sensorsmay fail, or provide faulty readings, the system as a whole maydisregard the high calibration data set from the sensors and may rely onmore general information from them, such as if weight is on the deviceor not. In such a system, and as may be used in general, the controlprogram may look at sensor readings only above or between set thresholdsin order to prevent stray or erroneous sensor readings from negativelyaltering the functions of the control program.

Still furthermore, it is understood that sensor data may be used inconjunction with other methods, equations, software, or the like, toextrapolate additional information such as but not limited to a methodof maintaining the center of gravity of the device or user to be overthe proper location of the foot via adjusting dynamically or passivelythe plantarflexion/dorsiflexion angle of the ankle, or resistancecharacteristics in general. This may require force sensor and/or angleinformation, amongst others to be analyzed to assess the forcedistribution, and force changing velocity in placement over the foot,gait cycle moments, and others.

Safety

In a preferred embodiment, numerous safety measures are constructed andprogrammed into the system. The below mentioned safety features are byno means exhaustive in nature. It is understood that numerous othersafety measures are taken, which may or may not be described in detail,which are necessary to maintain sufficient reliable and safe use of thesystem.

In pertaining to the force sensor threshold in particular, controlprogram should generally not allow the joint resistance, in particularankle in this example, to substantially lessen if the force value on thedevice is above a designated threshold. This may assist in preventingthe joint from too quickly loosening when the user intends for it toprovide stability, and cause a fall.

Still furthermore, the control system may provide a limit to the speed,angular velocity, or angular acceleration of the joint movement duringany or part of the gait cycle. In practical use, for instance, there maybe an angle change threshold limit built in to provide a limit to thespeed at which the angle is allowed to change according to the controlprogram in order to maintain a more consistent transition from one stateto another. This may be observed, for instance, after foot flat occurs,when weight is being applied to the foot. The ankle, in this example,may not be able to greatly, quickly, or otherwise largely lessen itsresistance until the lower force threshold is crossed, allowing thedevice to then transition more quickly to its next determined stage,such as after toe off in transitioning to the swing phase of gait. Thisthreshold may be set by the practitioner or patient, or may bepre-programmed into the system as a safety measure.

Still furthermore, through having an ankle joint that has the ability toaccommodate for alterations in force, speed, and terrain, safety is evenfurther improved. Through terrain accommodation for instance, as seen inFIG. 27A, the knee joint has inherently greater stability than what maybe found in an ankle joint that does not appropriately accommodate forterrain variance, FIG. 27B. Similar benefits may be found for speed andforce variations and accommodation through allowing the angle, angularvelocity, angular acceleration, angular resistance, and other variablesbeing most appropriate to best simulate natural biomechanics of not onlythe ankle joint, but also other joints such as the knee and hip.

Functions of Control Program

It is understood that the below explanations of the control system areto allow those skilled in the art of prosthetics, orthotics, androbotics to understand in detail what was submitted in the originalpatent application of this device. What is referred to as the DOUBLEHUMP GRAPH (though name should not be considered limiting, as the actualgraph may not have two humps) that was originally illustrated in thepatent application is characterized by the below descriptions. Thisfurther elaboration of explanation of that double hump graph is toassist those skilled in the art to understand its functions.

In a preferred embodiment, the control program should provide real-timecontrol of the damper, correlated to force, speed, and terrain changesin the environment. This may be accomplished in many different ways. Thebelow described goals and methods should not be considered limiting, butrather are illustrative of a possible method of implementation.

It is understood that the control program may work in conjunction with aprosthetic, orthotic, or robotic device to perform ambulationactivities. It is further understood that for a prosthetic, orthotic, orrobotic device, the control program may work in conjunction with anactuator system to control the general movement, force, speed,resistance, or other variables of the device or user. Still furthermore,the control program may be used in conjunction with active poweractuation strategies to further enhance functional abilities of thesystem.

1. Alter Midstance angle with respect to force alterations. In apreferred embodiment, as force on the system increases, Midstance mayoccur sooner, in angle or time, to provide increased pushoff or springreturn characteristics from the keel. It is further understood thatforce and speed of ambulation are highly related; hence Midstanceposition (angle or timing) may be altered according to speed ofambulation as well.

2. Alter Midstance angle with respect to terrain variations. Midstancemay occur at a similar angle with respect to level ground no matter theterrain. It should be understood that the angle between the shin andfoot may greatly alter for various terrains, but that the angle of theMidstance phase may be correlated to the terrain, whereas to provide amore natural Midstance resistance increase independent of the ambulatedenvironment. As will be further discussed below, the foot may be able tohave a compliant angular orientation to the terrain, while allowing anatural resistance of the ankle joint of the shin section at a naturalangle corresponding to the terrain angle.

3. Alter valve position with respect to force. As the force increasesfor instance, the valve position closes more during heel strike or footflat to midstance, midstance to heel off, and heel off to toe off, orwhichever combination thereof that is relevant for the increase inforce, in order to provide increased resistance to counter the force tomaintain angular velocity near appropriate levels. When more of lessforce is applied that typical, the gait dynamics may additionally bepurposely altered from normal ambulation characteristics by a certainfactor or amount as will be accounted for in the equations below tobetter accommodate for necessary biomechanics alterations given theincreased force. For example, as force increases, say when the user iscarrying a heavy load, it may be preferable to allow the ankle angle torotate during stance phase with higher angular velocity, angularacceleration, or a combination thereof, than with what would be foundduring normal ambulation. The converse of the same example mayoccur—with less force, and a more open valve position. The amount ofalteration to valve position according to a given force amount may bepredetermined, or learned through the control program.

4. Angular velocity may increase with increasing force, and decreasewith decreasing force. As force may increase, and valve position closesmore, it may be closed at an amount slightly less than necessary tomaintain constant, similar, or adjusted angular velocity with respect toa normal force. This may be experienced, for instance, during running,when a greater force is experienced during the gait cycle, valveposition is closed correspondingly to the increased force, but the finalvalve position may be altered slightly to provide a slightly higherangular velocity than would be tend to be experienced during normalwalking, so as to better accommodate for a faster transition through thegait phase defining points needed in running. This may be a linear ornon-linear function, and may be, in general, characterized by (constantangular velocity+function (angular velocity)). This may as well becharacterized by the general function of N/X in the included equations.

5. The control program may as well offer a learning algorithm to adaptto the user over a longer period of time. Functionally, this may changethe average angular velocity long term to effect midstance angle andvalve position settings.

6. The control program may provide static and dynamic cosmetic benefitsto the prosthetic system. The invention as a whole appropriatelyreplicates biomechanics in all conditions and in all environments duringdynamic movement—through accommodating for force, speed, and terrainchanges. Additionally, the system offers plantarflexion during sitting,for instance, which results in a static cosmetic appearance that is morelife-like than with conventional systems. Other custom tailored cosmeticrelated movements may be programmed into the system, which may or maynot provide ambulatory functional significance, but that may allow for amore enhanced cosmetic appearance in general.

7. The control program may approximate or replicate normal angularvelocity and general motion during ambulation throughout the varioussegments of the gait cycle, given no change in force, terrain, or speed.Functionally, the system will replicated the natural biomechanics of thespecific individual's gait pattern. As described above, the system mayalso alter its angular velocity changes in order to accommodate forforce, speed, and terrain changes. The control program settings may bemanipulated by the practitioner or patient to provide a symmetricallyequivalent gait pattern to the user.

Defining Points Definition

It is understood that there may be a plethora of variations or forms ofnoting the occurrences of the following descriptions of defining pointdefinitions and therefore should not be considered limiting. Each of thegait cycle defining points occurs during normal ambulation, and theassociated sensors, and their given combinations of data singly or incombination, may provide sufficient information to determine when, intime or angle, each of the defining moments occurs. The belowdescriptions may be used for general illustrative purposes to allowthose skilled in the art to understand the general functions of thecontrol program, and should not in any way be considered limiting.

In addition, in a preferred embodiment, when myoelectric or othercentral nervous system to prosthesis interaction takes place, signalanalysis, EMG data, pattern recognition, or other similar methods may beused to determine intended movement, and therefore intended definingpoints during the gait cycle. It is understood that nerve or musclesignals may characterize intended movements of the limbs, and thatinformation may be used to control the movement parameters of theprosthetic limb with enough definition to characterize the definingpoints. The following descriptions may illustrate a preferredembodiment, for little to no interaction with the central nervous systemof the body, but alternative or complimentary approaches may be used aswell as other neural signals may become available.

Direct Neural Control

Taking information from the user through sensors, versus solely throughsensors in the device, may control the limb directly through directneural control, or may control the limb through enhancing the functionsof the control program, or a combination of both. Methods of capturingintended movement data from the body's central nervous system mayprovide information to the microprocessor, or its equivalent, which mayallow for direct control of the prosthesis. In this case, the sensor orequivalent devices information may be provided to the controller. Thecontroller may provide a predetermined or alterable correlation betweenthe neural control data and the movement of the prosthesis, orthosis, orrobotic device. As the user initiates a neural response for intendedmovement of the device, the device may exhibit that similar movement.

Heel Strike

Heel Strike may be defined by angular change in plantar direction, anytime during the gait cycle, or during a selective period during the gaitcycle. Alternatively, it may be defined by certain other timing,angular, or other ordered parameters.

Heel strike position 206 cushioning and invention 10 plantarflexioncomes about mainly though true ankle plantarflexion and not simplythrough heel compression. It should be clearly understood that thecontrol program detecting angular change in the system is functionallyequivalent to detecting force, such as heel load or toe load forcesbecause there is a correlation between heel or toe load forces, andangular change given a set valve position. The two terms therefore maybe used interchangeably. While the heel portion of the keel 26 maycompress slightly, the ankle joint assembly 16 plantarflexion willconstantly be monitored to provide fluid, smooth, roll-overcharacteristics and provide optimal push off characteristics throughkeel 12 loading. As heel portion 26 load, moment sensor 192, or heelsensor system 174 or angular change sensor detect contact, footplantarflexes with angle/time angular velocity using damperplantarflexor resistance. As the force of heel portion 26 contactincreases, the damper resistance will increase to limit the force ofplantarflexion and offer controlled plantarflexion.

It is contemplated that this will generally simulate the tibialisanterior essentric contraction in human biomechanics at and soon afterheel strike position 206. Once the toe portion 34 load sensor 194 or toesensor system 176 is greater than or near zero at foot flat position208, the angle sensor 190 or sensor system 22 in general may predictangular change per time for heel portion 26 strike pressure sensor orheel sensor system 174. If angle/time is too slow, according to heelportion 26 strike pressure or heel sensor system 174, damper resistancedecreases. This would generally correspond to the slowing down of gaitspeed. If angular change increases with respect to previous step (goingdown a hill for instance), damper may keep plantarflexing until toeportion 34 load sensor or sensor system 176 is greater than zero.

It is contemplated that invention 10 will generally adapt to thesurrounding environment automatically, in order to maintain properstability, safety, and function. A similar effect would occur if theuser were wearing a high-heeled shoe. It should be noted that at heelstrike position 206 with many other prosthetic feet designs, theplantarflexion movement is obtained through heel compression. In apreferred construction, invention 10 may allow slight compression forshock absorption and smoothness of gait, but just as occursbiomechanically, the plantarflexion movement occurs through the anklejoint assembly 16 movement with an eccentric contraction of the tibialisanterior and not necessarily entirely through heel compression. It iscontemplated that, the dampening system 18 allows for the controlledplantarflexion, mimicking the tibialis anterior movement, while the heelor heel portion 26 compression may mimic natural heel fatty padcompression for general shock absorption.

Foot Flat

Foot Flat may be defined by an angular direction change fromplantarflexion to dorsiflexion. Alternatively, it may be characterizedby certain other timing, angular, or other ordered parameters, such asbut not limited to when toe load force exceeds set value.

With increased heel sensor 174 pressure or angular velocity during heelstrike position 206 to foot flat position 208, damper dorsiflexionresistance may increase from foot flat position 208 to midstanceposition 210 in order to provide increased plantarflexion during laterportions of gait to allow increased spring off from invention 10 fromheel off position 212 to toe off position 204. This may mimic the actionof the gastrocnemious muscles during walking.

Mid Stance

Mid Stance may be defined by taking the average angular velocityexperienced from heel strike to foot flat, subtracting the averageangular velocity historically from heel strike to foot flat. Dividingthat sum by X1 degrees per second. Multiplying that sum by N1. Adding tothat the sum of the Foot Flat angle experienced minus the Foot Flatangle level ground plus the Mid Stance GUI setting. The Foot Flat anglelevel ground may be a GUI set parameter or may be self-learned throughthe control program, or a combination of both. The Foot Flat angleexperienced may be the angle that Foot Flat occurs. This may becorresponding to the Foot Flat angle level ground plus the terrainangle. Furthermore to illustrate, in a preferred embodiment, what X1 andN1 are: For every X degrees per second difference in average angularvelocity experienced between heel strike and foot flat for instance,minus average angular velocity historically between heel strike and footflat for instance, change angle of Mid Stance by N degrees. This shouldfunctionally be a relatively small number. This equation accounts forboth changing Mid Stance according to force alterations as well asterrain alterations. Each component may be used in conjunction with theother, or independently.

The term average angular velocity experienced between heel strike andfoot flat for instance should not be considered limiting, and may bereplaced by other sensor data to provide similar function.

Average angular velocity historically between heel strike and foot flatfor instance, may be characterized by taking α(ω1 (i−1)+(α−1)Avg ωexp(HS−FF), where α equals the factor of length of average decreasing, ω1equals the average angular velocity historically from Heel Strike toFoot Flat for instance calculated previously, i equals current step, and(i−1) equals previous step.

It should be clearly understood that there are a number of mathematicalmethods of characterizing an average from a set of data, and what isbeing described is meant for descriptive purposes of how an average maybe calculated for a given set of data for use in prosthetics, and shouldnot be considered limiting. There are a number of alternative methods ofcalculating an average such as but not limited to taking the sum ofvalues, and dividing by the number of values. In such as case, eachvalue may have a relatively equivalent significance in correlation tothe others. Equivalently, taking a random set of values, or equallyspaced values (one out of every 1000 for instance) from a sequentiallist of values may be used to capture the data set for taking theaverage as well, amongst other methods. Methods as described in taking amoving or sliding average may be used to, in real-time, characterize themost appropriate characteristics of the user's gait pattern.Additionally, taking a non-linearly characterized significance of thevalues in a data set for taking an average may be used to better defineshort term or long term necessary alterations in the gait pattern ascontrolled by the control program. For instance, the user may gainweight over a several month period, and the average angular velocityhistorically value may be altered to account for that weight change.Additionally, a secondary component to the above equation may be used tocharacterized short term alterations such as if the person begins torun, and therefore the shorter term sliding average may account foraltering the gait pattern characteristics based off of the most recentsteps data set.

Still furthermore, the general control equations should not beconsidered limiting, as they depict one variation of illustrating suchcontrol parameters. Terms such as heel sensor system for instance,amongst others, should not be considered limiting, and can beillustrated in various embodiments such as but not limited to straingauge(s), calculated force value out of other sensor input(s), or otherforce related sensor values.

With increased heel portion 26 sensor pressure or generally indicationfrom heel sensor system 174 or angular velocity during heel strikeposition 206 to foot flat position 208, damper dorsiflexion resistancemay increase to provide increased plantarflexion during gait until toeportion 34 load sensor or toe sensor system 176 equals zero during toeoff position 204, or angular velocity equals zero, given open valveposition. It is contemplated this may allow slight dorsiflexion to acertain angle for smoothness of gait but may remain in someplantarflexion for push off from heel off position 212 to toe offposition 204. During this section of gait, the dampening system 18 maylock out to provide the necessary plantarflexion for push off; however,the angle which the dampening system 18 of ankle joint assembly 16 maylock out will vary according to angular sensor 190, heel load sensor 192during heel strike 206, and angular velocity determination, etc. It isfurther contemplated that the system may not fully lock out the damper,but rather, may provide a sufficiently stiff system in order to provideonly minimal angle change. During this portion of gait, the invention 10may go into some dorsiflexion, however, the dorsiflexion is obtained ina preferred embodiment through keel 12 loading and some ankle jointbending, therefore leading to increased push off at toe off position204.

Functionally, through the above equations, midstance may be set at moreor less angle with respect to what may be otherwise observed, given achange in force per step, as well as through changes over a longerperiod of time. This may use a multiplying factor not provide anon-linear relationship between force changes and produced angularvelocity changes from normal ambulation. Additionally, midstance maychange in angle corresponding to terrain.

Reel Off

Heel Off may be characterized by a GUI setting of p degrees past MidStance and may include other sensor information such as with toepressure above threshold. Utilizing data such as toe pressure abovethreshold may be used to prevent the system from accidentally becomingtoo instable for the user while weight is being applied. It may also becharacterized by a set time past Mid Stance, or force past Mid Stance.Alternatively, it may be characterized by certain other timing, angular,or other ordered parameters.

In natural human locomotion, the plantarflexor muscles fire at thisstage in the gait cycle to maintain ankle angle or provide slightplantarflexion for push off. It is contemplated that through invention10, the plantarflexion is already obtained through the midstance phaseof gait and having the dampening system 18 lock out or near lock out ata preferred or certain angle; however, it has been stored through keel12 loading and is released in spring off from heel off position 212 totoe off position 204 thus simulating gastrocnemious inducedplantarflexion of the foot.

Toe Off

Toe Off may be defined by when force experienced on the system droppingbelow a certain threshold. Alternatively, it may be characterized bycertain other timing, angular, or other ordered parameters.

After heel portion 26 load sensor 192 equals zero and/or toe portion 34pressure sensor approaches zero or a set threshold, or angular velocitywith valve position is such that force is near zero, damper resistancegoes to zero, or other low damper resistance setting and allows fordorsiflexion spring system 137 to dorsiflex foot during swing phase.

Equivalently, an active powered system or augmented powered system maybe used to assist in foot and ankle dorsiflexion.

Generally referring to FIG. 13, as the user completes the toe offposition 204 of the gait cycle, the dorsiflexion spring system 137, orcomplimentary dynamic alteration of joint angle may cause invention 10to immediately begin to go into dorsiflexion, as occurs in normal humanlocomotion, to decrease the likelihood of stubbing the toe portion 34during swing phase of gait. The term dorsiflexion spring should not beconsidered limiting, and in general, describes a method of passively oractively adjusting the ankle joint into dorsiflexion. Once full orpredetermined swing phase angle occurs, resistance of dampening system18 remains at or near zero or other predetermined valve setting, tomaintain angle or angular change, until heel strike position 206 whenheel sensor system 174 detect pressure or load greater than zero, orangle change is in plantar direction. The rate of dorsiflexion anglechange can be programmed to allow for optimal safety and symmetrythrough varying the valve position.

The spring load resistance of dorsiflexion spring system 137 may bemodified or changed through adjusting the spring drive length, changingto a lighter or heavier spring, altering the dorsiflexion actuationcharacteristics in general, and/or through increasing dampening system18 resistance, in order to optimize this characteristic for the user'sactivities. Furthermore, dynamic movement of the dorsiflexion system maybe adjusted through software, mechanical, fluid dynamics, or othermeans. By example, if the user intends to run, the dorsiflexion springsystem 137 resistance characteristics may be increased to overcome theinertial effects of the invention 10 during running. This may beautomatically accounted for through the control program or throughexternally adjusted means. Still furthermore, the dorsiflexion spring ormethod may work in a compressive or extension orientation, and mayactively pull or push the device into dorsiflexion.

Throughout swing phase, invention 10 may remain in dorsiflexion untilheel strike position 206 in order to generally shorten the extremity.

Furthermore, for midswing detection—this may use information of when toeoff occurs, quickly bringing system into dorsiflection at apredetermined, or alterable rate. Can also use predetermined valveposition of swing phase, compare angular velocity of device once in thatvalve position to what is typically found, possibly through an averagingmechanism, and alter the valve position accordingly to enable the footto dorsiflex faster or slower. If the user is running for instance, thependular effects of the foot may limit its ability to dorsiflex, so theangular velocity of dorsiflexion is too slow, and valve position opensup, and allows for it to dorsiflex faster. This provides a variableswing phase control. Can also use angular velocity within a certaintimeframe within the beginning of the swing phase and then alter afterthat given time frame. Then, look at new angular velocity with new valveposition, and compare to predicted or preferred angular velocity. Systemmay store that value and use it to alter the “intended” angular velocityover time. It may learn the user's walking style. For instance, if theankle is set it to dorsiflex at a certain rate, and the user begins towalk harder or faster and the foot is dorsiflexing too fast, the valveposition may change during the step to slow it down, but if that stilldoesn't slow it down enough, system may learn to put valve position alittle further to slow it down further next time—predicting gait style.

Valve Position Settings

Heel Strike or Foot Flat to Toe Off valve position settings may becalculated by taking the average angular velocity experienced betweenheel strike and foot flat for instance, minus the average angularvelocity historically between heel strike and foot flat for instance,and dividing that by X2 degrees per second. Then multiplying that valueby N2 and adding GUI valve position setting for HS, FF, MS, HO, or TO,given the gait cycle phase.

Equivalently, this may be characterized as well by taking Heel Strike orFoot Flat to Toe Off settings by taking the average angular velocityexperienced between heel strike and foot flat up to current moment intime or angle for instance, minus the average angular velocityhistorically between heel strike and foot flat up to current moment intime or angle for instance, and dividing that by X2 degrees per second.Then multiplying that value by N2 and adding GUI valve placement settingfor HS, FF, MS, HO, or TO, given the gait cycle phase.

Equivalently, force sensor information may be used to determine valveposition setting from heel strike to toe off, and from toe off to heelstrike. Even more, neural input from the user to the prosthesis may beused to characterize valve position setting during ambulation.

Functionally, the provided angular velocity of the angle change may bealtered according to force, whereas force increases, the angularvelocity may be allowed to increase during portions of the gait cycle ina linear or non-linear manner. This may be accomplished by opening orclosing valve position more or less corresponding to sensor data offorce, speed, or other measurable parameters.

Standing Up

When a user begins to stand, the control program may realize that weightis being applied to the foot, the foot may be moving in theplantarflexion direction, or begin to move in the dorsiflexiondirection, in which case the resistance will inherently increase.Functionally, this provides increased resistance on the toe portion ofthe prosthetic, orthotic, or robotic system, and inherently providesincreased knee extension moment. This may be beneficial to a variety ofusers who suffer from poor balance or knee stability or strength. For anabove the knee amputee for instance, this will greatly assist inproviding stability and safety when going from a sitting to a standingposition.

The amount that the foot goes into dorsiflexion upon standing may becustomized in the GUI settings, and the control program may use varioustiming and sensor information to analyze that the user was in factsitting, and is now attempting to stand.

Alternatively, the system may allow for slight dorsiflexion during thistime in order to allow the user to get their weight underneath them moreto better assist in standing. Through the GUI settings, the practitionerskilled in the art may be able to customize this parameter to the user.

Stumbling

The control program may as well determine that a user is stumblingthrough sensor input to the device, such as but not limited to having another than normal sequence of gait defining moment events, and mayaccommodate for stumbling actions through determination of other sensorsignals, and may generally dorsiflex foot during swing, move otherjoints such as knee or hip into general angle or with general force,provide increased resistance to device upon contact, or other. This mayadvantageously be used to predict intended movement to providestability.

Dynamic Data Capture for Control System

Additionally, the control program may use dynamic or static roll-overcharacteristics data to help determine ankle, knee, hip, or anycombination thereof, movement. Additionally, this information may beused to custom fabricate the structural members, such as the keel, andothers, to best tailor to the user. This data may come from the user'ssound side, or from a donor's gait cycle data, or a combination of both.This information may be further utilized to determine foot size, shape,and other characteristics to determine how much dorsiflexion, forinstance, the system may go through from foot flat to toe off. Thecontrol program may use this data to emulate the natural roll-overprogression characteristics, including but not limited to heel, ankle,and forefoot rocker dynamics. Furthermore, the system may utilize acombination of GUI settings, control program equations, and sound sidegait data to best tailor the specific movements of the prosthetic sideto match the sound side. This may come about through wearing the sensorson the sound side during ambulation on the prosthesis, or may come aboutthrough data capture from the user's sound side and then importing thatdata to the prosthesis for control or movement alterations thereof.

Still furthermore, the data captured from the sound side foot may beused to determine 0 characteristics (thickness, stiffness, etc.) of theprosthetic keel. It may as well be used in the fabrication process,including rapid prototyping of the form to make the keel, as well as topossibly make the keel itself. The general attachment method of the keelto the ankle device may be standard so that all custom keels may matchto the ankle unit. It may be important to provide custom keels to theuser because the foot plantar surface characteristics, including arches,surface area, rockers, and other characteristics influence the gaitdynamics.

Research may then be done on the performance and gait analysis of anamputee walking to compare differences in sound and prosthetic sidegait. This may help to further refine the system to best match theuser's optimal performance.

In one embodiment, the controls may be implemented using multiplexoperation of joint actuators. The system may consist of a control boardand a multiplexer board. The control board may send address signal tomultiplexer board to enable/disable ground place of each actuator. Thefeedback (which may be deflection amplitude) may then be connected tocontrol board. Each motor may be connected in series or parallel withthe control board. The driver and on/off signals for the motors may begenerated through a field programmable gate array. The driver circuitmay use a push pull converter consisting of gate driver, power switches,and transformers. The control board may use a microcontroller or amicroprocessor. The control parameters may be changed using a graphicaluser interface using Matlab, Labview, Visual basic, or any othergraphical or non-graphical programming environment. The filter designmay have 1 KHz cutoff frequency or other frequency ranges. For highspeed data-bus a serial SpaceWire protocol may be used or other similarforms. For switching power to the actuators, FETs may be used. Forreversing the direction of motor a speed profile may be used. Differentlevels or frequency/amplitude may be used to finely control the speedand reduce the power requirement when moving the coordinated joints.

Thermal Viscosity Alterations

The issue of changing thermal viscosity may be inherently resolvedthrough the portion of the control program equation of average angularvelocity experienced from heel strike to foot flat for instance becausein such an equation the average angular experienced is changing withrespect to viscosity and hence altering valve position setting tocounter the fluid being more or less viscous than when programmedoriginally. Alternatively, an additional equation may be added with asmaller population pool in taking the average to take a new average overrecent steps only to account for viscosity changes to the fluid. Stillfurthermore, additional sensor system(s) may be incorporated into thedevice to assess fluid viscosity or temperature, and allow the controlprogram to account for that change accordingly.

Further Equation Definitions and Methods

Furthermore, control system equations and data, including gait cycledefining points as illustrated in FIG. 26 may be depicted as, but notlimited to the following: Equations:

Mid-Stance Angle Calculation

$\theta_{Ci} = {{\frac{N}{X}\left\lbrack {\omega_{i} - \omega_{a}} \right\rbrack} + \theta_{Ei} - \theta_{L} + \theta_{M}}$

Foot-Flat to Mid-Stance Damping Calculation

$B_{ffi} = {{\frac{N}{X}\left\lbrack {\omega_{i} - \omega_{a}} \right\rbrack} + B_{FFU}}$

Mid-Stance to Heel-Off Damping Calculation

$B_{MSi} = {{\frac{N}{X}\left\lbrack {\omega_{i} - \omega_{a}} \right\rbrack} + B_{MSU}}$

Heel-Off to Toe-Off Damping Calculation

$B_{HOi} = {{\frac{N}{X}\left\lbrack {\omega_{i} - \omega_{a}} \right\rbrack} + B_{HOU}}$

Definitions

ω_(i)=Peak angular velocity from heel-strike to foot-flat during onegait cycle (i)

ω_(a)=Average peak angular velocity from heel-strike to foot-flat.

m=Number of gait cycles for averaging

X, N=User constants

θ_(Ei)=Foot-flat experienced during one gait cycle

θ_(L)=Foot-flat level ground user setting

θ_(M)=Mid-stance user setting

B_(FFi)=Foot-flat to Mid-stance damper calculation during one gait cycle(i)

B_(FFU)=Foot-flat to Mid-stance damper user setting

B_(MSi)=Mid-stance to Heel-off damper calculation during one gait cycle(i)

B_(MSU)=Mid-stance to Heel-off damper user setting is indicated as

B_(Hoi)=Heel-off to Toe-off damper calculation during one gait cycle (i)

B_(HOU)=Heel-off to Toe-off damper user setting

Notation: Plantar direction is defined as positive.

Gait Cycle Indicators

-   -   Heel strike event—negative to positive (plantar) direction        change    -   Foot flat event—positive to negative (dorsal) direction change    -   Mid-stance event—Occurs on reaching the calculated mid-stance        angle    -   Heel off event—Occurs on reaching the user specified angle        forward of mid-stance    -   Toe off event—Occurs on losing toe force        -   a. Non-gait indicators    -   Toe-load—toe force used as indicator for toe-load at which time        the prosthetic is required to prevent falling    -   Heel-strike—used in other gait stages to indicate a new gait        cycle beginning

Still furthermore, FIGS. 30, 31, 32, 33, and 34 generally may depictpossible preferred embodiments of control system flow diagrams andgeneral methods of functioning, but should not be limited to such.

Furthermore, the force sensor, for the control system function, maysimply be utilized as an on/off switch to determine if force is on thefoot or not. Additionally, other sensors may be used instead to providecontact information only.

Still furthermore, sensor signals may be filtered to produce more usabledata. Additionally, for use in historic biomechanics data capture, theuse of autoregressive, moving average, autoregressive moving average,autoregressive integrated moving average, low or high pass, otherregressive methods such as but not limited to linear, quadratic,exponential, harmonic, ordered polynomials, or other methods may beused.

The defining moments may as well occur in other than normal orders in apreferred embodiment, and is not dependent on using sequential definingpoints order for proper function.

Electronics

The electronics flow chart diagrams, and general methods ofimplementation may be illustrated by the FIGS. 30, 31, and 32 but shouldnot be considered limited to such. Other illustrations and embodimentsare conceived as well, not departing from the spirit and scope of thedisclosure.

Modular Robotics

In a preferred embodiment, the functional characteristic of a computercontrolled prosthetic, orthotic, or robotic ankle or foot may work inconjunction with other joint such as a knee and/or a hip, but notlimited to such. Each of the joints that are developed may have theability to function alone or independently from others when necessary,but may as well be able to function in conjunction with other joints toprovide enhanced control or functions. Any communication that may takeplace between various joint may be through wires or wireless means.

Furthermore, a computer or electronically controlled joint system may aswell utilize an array of various control programs, specificallycharacterized for given patient needs. For instance, some users of theprosthesis will have the functional ability to do little more thantransfer on the prosthesis, orthosis, or robotic device, or evenpossibly walk with assistance, while others may be very active andtransverse ramps, barriers, stairs, or other activities with ease andstability. It is contemplated that the mechanical characteristics of thespecific joint may be equivalent or similar for many users, such asrange of motion, resistance range (fully locked to fully unlocked forinstance), and others, while the functional characteristics such as butnot limited to control methods, stability requirements, assistancemethods, augmented power levels, and other parameters may be modularlyaltered according to the user's needs. In such a case, the type ofspecifics of the control program may be specified in order to allow thespecific user to have optimal biomechanics, stability, safety, ease ofuse for certain activities, or other adjustable reasons. Stillfurthermore, the use of communication in general of or between variousjoints may further add to the functional benefits of given users.

It is contemplated that the functional parameters of a prosthetic kneefor instance may be correlated to information based off the foot orankle parameters to enable the knee to function in a more preferredmethod. Equivalently, the hip function may benefit from informationbased off of ankle and/or knee information.

Still furthermore, a prosthetic, orthotic, or robotic knee or hip jointmay as well encompass the equivalent or similar electronics, circuitdesigns, control programs, control parameters, communication system,neural input methods, including pattern recognition, to control or usesuch a device. It is contemplated that the usage of such describedsystems in a knee or hip are considered equivalent and complimentary toan ankle mechanism, and should not be considered limiting, and should beconsidered as one and the same as the ankle illustrations and methods ofsuch a device.

Alterations from Normal Ambulation Function Plantarflexion In Sitting

A common complaint of many prosthetic foot users is that theirprosthetic foot “sticks up” when they sit. This un-cosmetic appearanceis eliminated through invention 10 by allowing the prosthetic to loseall or much of the plantarflexion resistance when the user is sitting,thus, allowing the foot to be at a natural angle. In a preferredconstruction, it should be noted that the dorsiflexion spring system 137should not provide too much resistance to plantarflexing as to preventthe necessary motion in sitting, or to alter the gait patternnegatively. During sitting, it is contemplated that the dampening system18 may prevent dorsiflexion while allowing plantarflexion to be free inorder to provide greater cosmetic appearance. The sensor system 22(time, angle, moment, etc.) may determine if the user is sitting andwill correspondingly allow invention 10 to plantarflex.

It is also contemplated that heel pressure, as generally determined byheel sensor system 174, that occurs for a given time period such as afew seconds, with no toe pressure, as generally indicated by toe sensorsystem 176, may indicate or allow plantarflexion for sitting whereinlittle to no resistance is created. Still furthermore, sensor system mayallow, during sitting, for the foot to naturally plantarflex with heelstrike to foot flat resistance setting, until sufficient toe pressure isreached, and may in general prevent the foot from dorsiflexing until therequirements for doing so are met as would be found during ambulation.This as well may provide increased stability during standing back up orto provide increased knee stability for use in a transfemoral or hipdisarticulation level amputation.

Still furthermore, the plantarflexion characteristics of the foot duringsitting, and standing may be actively altered through a powered systemin real-time, as necessary to provide optimal stability and safety forthe user.

It is further contemplated that a negative bending moment on the heelportion 26 could signal the microprocessor unit 172 that the user hassat down and to have free plantarflexion abilities. A preferredembodiment may be by planting the heel portion 26 into the ground aftersitting and pulling back. This action would generally not occur innormal walking and may therefore be a sufficient indicator for sittingaction. Other methods of actuating plantarflexion in sitting may be usedas well.

Heel Height Adjustment Accommodation

In a preferred construction, invention 10 is constantly updating thesensory feedback system 22 information to the microprocessor unit 172wherein the user can change heel heights of a shoe without changing anysettings. If the user goes to a higher heel height for instance, thesensors system 22 will still read the moment forces and consider thatthe user is equivalently merely walking down a hill and, thus, the gaitof the user will not significantly alter, for instance. In this case,the ankle joint's angle and timing of resistance is appropriatelymatched to the sound side's movement. The dampening system 18 canfurther be designed to allow a certain amount of heel height clearanceaccommodation. It is contemplated to allow about 15 degrees ofdorsiflexion and about 45 degrees of plantarflexion to allow propernatural human locomotion and to allow for heel height changes. It isfurther contemplated that more or less degrees of rotation may bedesired to allow for more or less of a range of motion to achievenatural human locomotion. It is understood that natural human locomotionmay be altered or generally defined by such things as a user's desire orneed to wear higher or lower heeled shoes.

In a preferred embodiment, invention 10 may have special modes to allowthe user to lock the keel 12 or joint assembly 16 out at a given angle,such as for skiing, or can change the characteristics for other specificactivities where limited motion is required. It is understood thatvarious methods of implementing such is contemplated. Still furthermore,the use of inherent compliancy built into the system, may provide for amore natural feel during such activities.

Stumbling or Walking Up Steep Hill

If toe load sensor 194 is greater than zero before heel load sensor 192is greater than zero, then damper resistance may remain at or near zeroor may fully lock up to stabilize joint assembly 16 if not fullydorsiflexed already, to continue to allow for full dorsiflexion viadorsiflexion spring system 137. In walking up a hill, this movementwould still be similar to natural human locomotion and may benefit theuser by decreasing or reducing hyperextension of the knee, as is foundin the prior art. The use of active powered, or augmented powered systemmay as well be implemented to provide alterations to the plantarflexionor dorsiflexion state for such activities, such as but not limited toaltering the ankle angle during such activities.

Walking Down Hill

As angular sensor 190 determines that there is a greater angular changesince heel strike position 206 and foot flat position 208, wherein toeload sensor 194 maybe greater than zero, invention 10 may provideslightly less dorsiflexion resistance from heel off position 212 to toeoff position 204 to allow the user to descend downhill according toproper natural human locomotion. The use of active powered, or augmentedpowered system may as well be implemented to provide alterations to theplantarflexion or dorsiflexion state for such activities.

Going Up Stairs

It is understood that generally a foot will already be in dorsiflexionafter previous step and may remain in dorsiflexion as the stairs areascended. Of note, invention 10 may or may not provide active push offduring ambulation, on each step, providing the optimal keel 12 angle toenhance push off characteristics during gait. Thus, invention 10generally may allow for the greatest anterior support and energy returnper walking speed and environment.

In going up stairs, biomechanically, active push off is achieved withgastrocnemious muscle activity. It is contemplated that invention 10 maybe modified within the scope of the claims and description such that agenerally heavier design with increased power output consumption maygenerally simulate the natural muscle activity in this action. In such acase, the use of active powered, or augmented powered system however mayas well be implemented to provide alterations to the plantarflexion ordorsiflexion state for such activities.

It is further understood that in ascending stairs, the foot naturallygoes into dorsiflexion for the first half of the ascent. A separatesetting may also be included or programmed whereas the user may placethe invention 10 in “stair ascent” mode to allow slight plantarflexionor, if preferred, less dorsiflexion, or similarly, active poweredactuation through a range of motion.

It is understood that during stair ascent, the foot contact is made insome dorsiflexion, of which the foot is already in dorsiflexion duringthe swing portion of the gait cycle. The foot may then be allowed tocontinue into increased dorsiflexion at a set or variable dorsiflexionrate according to other sensor data such as but not limited to heel offsensor, angle sensor, or others. This biomechanical action is requiredfor proper motion during stair or hill ascent. Toward the end of thestep, the foot may go into powered plantarflexion, in accordance withspring or powered actuation strategies.

Going Down Stairs

It is contemplated that if heel sensor 174 load or strike sensor 192 isgreater than zero two steps or times in a row and no toe sensor 176 loador strike is observed, resistance in damper may increase at foot flatposition 208 angle to prevent full plantarflexion and slipping off step.Still furthermore, as with the other ambulations generally describedabove, microprocessor unit 172 may be calibrated specifically for a userafter a test run, sample, or base line is established of user performingthe ambulation in an optimal manner. It is contemplated that by allowingthe foot to plantarflex, invention 10 may improve ambulation indescending stairs. The use of active powered, or augmented poweredsystem may as well be implemented to provide alterations to theplantarflexion or dorsiflexion state for such activities.

During stair descent, the foot may be put into plantarflexion prior toground contact through neural integration strategies, sensor input,powered actuation methods, or environmental feedback, amongst othermethods, and then provide resistance to dorsiflexion upon contact.Additionally, it may provide powered plantarflexion during the step.

Graphical User Interface System

In a preferred embodiment, custom tailoring of the dynamiccharacteristics of the prosthetic system may be produced through agraphical user interface system, or the like. This system may encompassa computer based software for a desktop or laptop computer, it may besoftware that is managed through a cell phone or PDA, it may beaccessible through a handheld electronic device or key fob, or may bemanaged through another form of electronic user interface. The abovedescription is not meant to be considered limiting in any way, butrather, generally illustrates possible interaction methods of the userto the prosthetic device from a setting perspective.

Who has Access

The user interface may include the ability for the practitioner,patient, or others to alter the state of the device in numerous ways. Itis conceived that practitioners and patients may each have their ownunique set of possible adjustments. This may allow the practitioner tohave complete access to system variables, while the patient, forinstance, may have a limited set of adjustable variables. It may benefitthe patient by allowing them to more finely custom tailor theirprosthesis to meet their individual desires or requirements.Additionally, it may have psychological benefit to the user by havingbetter control of the functions of the system. Still furthermore, othersmay have access to the information from the interface system toextrapolate data based on the user's gait and usage, current orhistorical. If assessing current gait data, the biomechanics portion ofthe software may allow for real-time analysis much like how a gait labwould provide.

Still furthermore, the GUI may encompass settings for control of anankle/foot, a knee, and/or a hip joint, amongst others. Each of theabove mentioned joints may work in communication with one another orindependently, but the setting functions may be similar so that a commonGUI template may be used.

Structure of GUI

The graphical user interface (GUI) may be structured as a softwarecomponent installed separately from a disk, which is provided, to theend user or practitioner. Alternatively the GUI may be automaticallylaunched when the prosthesis system is connected to the computer via acommunications link. These descriptions are meant to be illustrative,not limiting the GUI to any particular installation or launch method.

The GUI may be composed of a set of images, which depict buttons, text,and other graphical elements on the computer screen. By interacting withthe elements, the user is able to effect changes to the prosthesissystem. Additionally, the user may be able to make changes in other wayssuch as with buttons or switches physically attached to the prosthesis,or through neural interface methods, or by any other method.

Functions of the GUI

The graphical user interface (GUI) may allow for manipulation ofvariables of the system. This may include settings for resistancevariables during various segments of the gait cycle. Additionally, itmay include adjustments to the control system equations, or variablesthereof. Still furthermore, it may allow for patient information, notes,pictures, biomechanics information and settings, usage information,graphical displays of various forms, warning settings, warningcommunications methods, internet access, gait lab information, andbattery level amongst others. The gait lab information may be providedin a graphical format, which depicts the values of the variables as theychange in time. This format may also allow the graphs to be superimposedfor comparison purposes. Additionally, the user may be allowed to rotatethe data in a three-dimensional view or zoom the display in or out.

The GUI may allow the user to control the feedback variables in theprosthesis as well. Additionally, the GUI may allow for a mechanism forthe user to unlock features of the prosthesis, which are only availablewith a special key.

Biomechanics Data

Biomechanical data may be analyzed through the GUI. This analysis mayinclude a full gait-lab-like assessment abilities. Information for thismay be visible by the user in real-time or through reviewing historicaldata. Additionally, there may be ability to overlay various layers ofinformation in various graphical or display forms to better assessinformation. Still furthermore, there may be ability to view video andgraphical displays in unison. Types of information that may be viewedmay be force, terrain, angle, speed, angular velocity, angularacceleration, video, all kinetic and kinematic information, numbers ofevents such as but not limited to steps, and other forms of information.This list is not meant to be limiting in any way but rather to provideillustrative purposes of available information. Still furthermore, theremay be customizable information assessment through tailoring graphicaldisplays. For instance, a graph of any number of variables may havethreshold bars, which may limit the range in which a certain variable(s)may be viewed. For instance, a graph showing number of steps per day maybe refined to view steps per day between certain hours or betweencertain terrain levels. This example is not meant to be limiting, but israther used for explanatory purposes only.

Numerous variables are able to be defines within this system to compareany other variable. Below is an elaborated illustration of examples ofvariables that may be selected. It is understood however that this is innot a comprehensive list and should not be considered limiting in anyway.

Biomechanics Lab System

-   1. Enables the User to set, alter, update, store, and retrieve    Patient's and Practitioner's Name as well as the date (Month, Day,    and Year) the Patient's file was last updated.-   2. Graph Manipulation:    -   a. Animation—Mobile real-time plotting of device extracted,        user-specified data    -   b. Toggle Animation on and off.    -   c. Select a static graph type from among the following: Pie,        Line, Bar, Cone, Area, Stock, Radar, Bubble, Column, Surface,        Cylinder, Pyramid, XY (Scatter), Doughnut, Area Blocks, B & W        Area, B & W Column, B & W Line (Time Scale), B & W Pie, Blue        Pie, Colored Lines, Column-Area, Column with depth, Cones,        Floating Bars, Line-Column, Line-Column (2-Axis), Line (2-Axis),        Logarithmic, Outdoor Bars, Pre Explosion, Smooth Lines, Stack of        Colors, Tubes, etc.    -   d. Display either 1, 2, or 3 graph(s) (unique, identical, and/or        same type or unique type) at once.    -   e. Display either 1, 2, 3, or 4 Joint(s) (unique, identical,        and/or same type or unique type) data on the graph(s) displayed.    -   f. Start Animation—Evoke (begin, launch) Animation.    -   g. Record Animation—Store Animation with time stamp for later        use.    -   h. Replay Animation—Retrieve and plot previously stored        (recorded) Animation.    -   i. Stop Animation—Stop (halt indefinitely) Animation.    -   j. Resume Animation—Continue Animation.    -   k. Pause Animation—Freeze Animation.-   3. Joint Record Manipulation:    -   a. Joint Specification:        -   i. Enables the User to select the Joint Record Number (Joint            #1, Joint #2, Joint #3, Joint #4) in order to denote the            specified Joint Record.        -   ii. Enables the User to select the Joint Type (Ankle, Hip,            Hand, Wrist, Elbow, Hand, Shoulder, etc.) with respect to            specified Joint Record.        -   iii. Enables the User to select up to 4 Joint Records            (inclusive) indexed by the combination of a Joint Record            Number and Joint Type as a key for the Joint Record.    -   b. Biomechanics Range Specification:        -   i. Enables the User to select Joint-Specific Biomechanics            Type parameters as follows:            -   1. Ankle, Hip, and Knee—Number of Gait Cycles, Number of                Stumbles, Amount of Force, Angle Occurrence, Amount of                Resistance, Angular Velocity, Step Length, Stance Time,                and Myoelectric Specifics.            -   2. Hand—Number of Actuations, Openings, Closings, Thumb                Adductions, Thumb Abductions, and Myoelectric Specifics.            -   3. Wrist—Number of Actuations, Flexions, Extensions,                Pronations, Supanations, Adductions, Abductions, and                Myoelectric Specifics.            -   4. Elbow—Number of Actuations, Flexions, Extensions, and                Myoelectric Specifics.            -   5. Shoulder—Number of Actuations, Flexions, Extensions,                Pronations, Supanations, Adductions, Abductions,                Rotations, and Myoelectric Specifics.        -   ii. Enables the User to select Joint Specific Range            Type/Terrain parameters as follows:            -   1. Ankle, Hip, Knee (Lower Extremity=>Terrain or Range                Type)—Incline, Decline, Level Ground, or All Terrains.            -   2. Hand, Wrist, Elbow, Shoulder (Upper Extremity=>Range                Type)—Force, Angle, Resistance, Angular Velocity.            -   3. Specialty Biomechanics Type-Specific Range Types:                -   a. Force—If this item is selected as a Biomechanics                    Type then the Range Types that are selectable are                    Angle, Resistance, and Angular Velocity meaning that                    the User is able to view a graph of the amount of                    force that is placed on the selected joint at either                    a single angle, resistance, or angular velocity or                    between two angles, resistances, or angular                    velocities inclusively.                -   b. Angle—If this item is selected as a Biomechanics                    Type then the Range Types that are selectable are                    Force, Resistance, and Angular Velocity meaning that                    the User is able to view a graph of the angle of the                    selected joint at either a single force, resistance,                    or angular velocity or between two forces,                    resistances, or angular velocities inclusively.                -   c. Resistance—If this item is selected as a                    Biomechanics Type then the Range Types that are                    selectable are Angle, Force, and Angular Velocity                    meaning that the User is able to view a graph of the                    amount of resistance that the selected joint                    produces at either a single angle, force, or angular                    velocity or between two angles, forces, or angular                    velocities inclusively.                -   d. Angular Velocity—If this item is selected as a                    Biomechanics Type then the Range Types that are                    selectable are Angle, Force, and Resistance meaning                    that the User is able to view a graph of the angular                    velocity that the selected joint produces at either                    a single angle, force, or resistance or between two                    angles, forces, or resistances inclusively.        -   iii. Enables the User to Select Range Type-Specific or            Terrain-Specific High and Low Range parameters as follows:            -   1. Ankle [Terrain (Incline, Decline, Level Ground, All                Terrains)]—Low Range (HS, FF, MS, HO, or TO) and High                Range (HS, FF, MS, HO, or TO), where Low Range is an                instance of occurrence less than or equal to the                instance of occurrence of High Range [i.e. Low Range=HS                then High Range=(HS, FF, MS, HO, or TO), Low Range=FF                then High Range=(FF, MS, HO, or TO), etc.].            -   2. Hip [Terrain (Incline, Decline, Level Ground, All                Terrains)]—Low Range (Flexion or Extension) and High                Range (Flexion or Extension), where Low Range is an                instance of occurrence less than or equal to the                instance of occurrence of High Range [i.e. Low                Range=Flexion then High Range=(Flexion or Extension),                Low Range=Extension then High Range=(Extension), etc.]            -   3. Knee [Terrain (Incline, Decline, Level Ground, All                Terrains)]—Low Range (Stance Flexion, Stance Extension,                Swing Flexion, or Swing Extension) and High Range                (Stance Flexion, Stance Extension, Swing Flexion, or                Swing Extension), where Low Range is an instance of                occurrence less than or equal to the instance of                occurrence of High Range [i.e. Low Range=Stance Flexion                then High Range=(Stance Flexion, Stance Extension, Swing                Flexion, or Swing Extension), Low Range=Stance Extension                then High Range=(Stance Extension, Swing Flexion, or                Swing Extension), etc.]            -   4. Force, Angle, Resistance, Angular Velocity—Low Range                and High Range are governed by the following: 0 units, 1                Unit, 2 Units, . . . Max Units, where Max Units are the                maximum Units of force, angle (degrees), resistance, or                angular velocity that can be experienced by a Joint and                Low Range is less than or equal to High Range.    -   c. Target Data Time Period:        -   i. Enables the User to Select Joint Record-Specific Time            Span Parameters as Follows:            -   1. Enables the User to Select Time Span scope [Per Day                (24 hours), Per Month (30 Days {30 Days Times 24                Hours}), Per Year (12 Months {12 Months Times 30 Days                Times 24 Hours}] parameters            -   2. Enables the User to Select Time Span Scope-Specific                quantity parameters as follows:                -   a. Per Day—1 day, 2 days, 3 days, . . . , 30 days.                -   b. Per Month—1 month, 2, months, 3 months, . . . ,                    12 months.                -   c. Per Year—1 year, 2 years, 3 years, . . . , 10                    years.        -   3. Enables the User to select a starting day (Month, Day,            Year) and computes the remaining span of events given the            Joint Record-Specific Time Span Parameter and the Time Span            Scope-Specific parameter.    -   d. Joint Record Manipulation:        -   i. Enables the User to select any combination of Joint            Record parameters over 3a to 3c (inclusive) within the            specified User utilization methodologies described above            (i.e. ankle-specific parameters combinated with ankle            specific selections, wrist-specific parameters combinated            with wrist-specific selections, elbow-specific parameters            combinated with elbow-specific selections, etc.)-   4. File Operations:    -   a. New—Enables the User to create a new patients data file. This        procedure clears the components of all forms associated with the        Biomechanics System software and resets the components input        data to their defaults. Note that the default inputs of these        forms consist of the data that appears or not in the        User-manipulatable areas of these associate forms as well as the        main Biomechanics System form.    -   b. Open—Enables the User to search, find, retrieve, and open to        form a previously stored (existing) patient Biomechanics file        from the hosting computer's file directory. Note that only files        with the “.” Extension having the Biomechanics System data        format are readable by the Biomechanics System.    -   c. Save—Enables the save [overwrite (store)] a currently open        (see 4b. above) and existing patient Biomechanics file to the        hosting computer's file directory.    -   d. Save As—Enables the User to search, find, retrieve, and open        or create a file folder and save (store) to directory a        non-existing User-defined and created patient Biomechanics file        in the hosting computer's file directory. Note that only files        created with the Biomechanics System automatically have the “.”        Extension having the Biomechanics System data format when stored        in the hosting computer's file directory.    -   e. Print—Enables the User to send the currently open (see 4b.        above) patient Biomechanics data file formatted, structured, and        well organized to a User-selected printer for output.-   5. Patient:    -   a. Enables the User to Set the Practitioner attending to the        Patient as well as the date (Month, Day, and Year) that the        Practitioner set by the User updated the Patient Form.    -   b. Enables the User to Set the Patient's Picture (Photo of        Patient), First Name, Middle Initial, Last Name, Date (Month,        Day, and Year) of Birth, Height (feet and inches), Weight        (Pounds and Ounces), and Social Security Number (9 numerical        digits).    -   c. Enables the User to set the Patient's contact information        [Address (Street Address, City, State, and Zip Code) and Phone        Number (3-digit area code, 3-digit prefix, and 4-digit suffix)]        and Practitioner comments about the patient.    -   d. New—Enables the User to Clear the form of the above [5a to 5c        (inclusive)] data.    -   e. Open—Enables the User to Open an existing Patient file        consisting of the above [5a to 5c (inclusive)] data and display        it to Patient form.    -   f. Save—Enables the User to Save (store) User constructed        Patient data consisting of the above [5a to 5c (inclusive)] data        from Patient form to a newly created patient file.    -   g. Save As—Enables the User to Save (store) User updated Patient        data consisting of the above [5a to 5c (inclusive)] data from        Patient form to an existing patient file.    -   h. Print—Enables the User to print the Visible Patient Data        consisting of the above [5a to 5c (inclusive)] data to a User        selected printer.    -   i. Get Picture—Enables the User to search through the directory        of files on the hosting computer and select a picture file        (“.jpg”, “.gif”, “.png”, “.bmt”, etc.) to display in the Patient        form. The selected picture file automatically displays once the        User selects and opts to open the picture file.    -   j. Exit—Enables the User to exit (close) the Patient form and        return to the Biomechanics Form (Main Form).-   6. Get Movie:    -   a. Enables the User to Render and manually (via mouse and/or        command buttons) manipulate three-dimensional animated and/or        static modal of joint under observation by the User by way of        the Biomechanics Form (Main Form).    -   b. Play—Enables the User to run (simulate animation) the        three-dimensional joint (in motion) in real-time as well as        utilizing stored data from a previous joint cycle.    -   c. Record—Enables the User to record (store) real-time joint        simulations from screen to file.    -   d. Replay—Enables the User to re-run (simulate animation) the        stored data from a previous joint cycle.    -   e. Resume—Enables User to re-evoke Play (denoted above in 6a)        after a Pause (denoted below in 6h) action taken by the User.    -   f. Rewind—Enables the User to back track currently Playing        (denoted in 6a above) data animation simulation to a specified        instance in time of the joint cycle.    -   g. Fast Forward—Enables the User to forward track currently        Playing (denoted in 6a above) data animation simulation to a        specified instance in time of the joint cycle    -   h. Pause—Enables User to stall current Playing (denoted in 6a        above) data animation simulation at a specified instance of time        in the joint cycle.    -   i. Stop—Enables the User to stop (halt indefinitely) the Playing        (denoted in 6a above) data simulation animation.    -   j. Exit—Enables the User to exit (close) the Movie form and        return to the Biomechanics Form (Main Form).-   7. Enables the User to launch, manipulate, alter, update, and share    both communication and data resources with other Martin Bionics    software designs such as Ankle System, Knee System, and Sensory    Feedback Systems.-   8. Advanced—Enables the User to set joint specific data parameters    to alter the state of the joint specified by the User with respect    to data storage and retrieval, timing, computation, simulation,    graphics display (static and animated), etc.-   9. Instructions—Enables the User to view structured and well    organized, step-by-step instructions for manipulating User-Specified    components and facilitations of the Biomechanics System Software.-   10. Training—Enables the User to both virtually and manually    simulate exercise interfacing with the Biomechanics system by way of    three-dimensional world manipulations and facilitations utilizing    physical prosthetic joints and computer input devices such as    keyboards, mouse, monitor, and/or connections to the USB port(s)    and/or COM port(s).-   11. Helb—Enables the User to access and read through a collection of    structured, well-organized, and formatted web documents (“.HTML”    files) which both describe the components of the Biomechanics    software in detail and provide step-by-step, detailed instructions    for facilitating User Interfacing with the Biomechanics System    software.-   12. Exit—Enables the User to Terminate (Exit indefinitely) program    Execution.

Transfer of Biomechanics Information

The biomechanics information and data may be stored in the ankleelectronics, software, microprocessor, or the like, and may betransferred to the GUI software, computer, or other internet site by anymeans known in the art of computing. This allows for stored usage dataof the device to be transferred to others for testing, research, andanalysis, statistical analysis, and data collection.

Still furthermore, the software may be updatable for the practitionersin the field or to the users of the device by connecting via internet orother means to download, or similar, the updated or renewed software. Ifeach time that the patient, or user's, prosthesis, orthotic, or roboticdevice is connected to the practitioner's or user's computer to adjustsettings or similar, the biomechanics or usage information isdownloaded, then when the new software is updated or renewed, it mayautomatically transfer that information for compiled research analysisof many users. This usage information may be valuable to a prosthetics,orthotics, or robotics manufacturer.

Still furthermore, connecting the GUI to a main computer may come aboutthrough wireless means, or wired means. If wired means are utilized, thedata connection port may be located through the proximal pyramid site.This may be a beneficial area to connect data through because it is wellprotected from the environment. Additionally, the connectivity site maybe located at any other area of the prosthesis.

Other Preferred Embodiments

Additionally, it is contemplated that invention 10 may be used inconjunction with myoelectric muscle contacts on the residual limb 404for trans-tibial amputees and may provide greater control in ambulation.By example, at heel strike, tibialis anterior or other complimentarymuscles contraction may be used to determine the level of damperresistance preventing or reducing too fast or too much plantarflexion aswould be found in eccentric muscle contractions during ambulation. Also,increased gastrocnemeous or other complimentary muscles contractionduring midstance may initiate dorsiflexion resistance sooner or stifferto allow keel 12 to remain in increased plantarflexion from midstance totoe off, therefore increasing push off may be utilized in fast walkingor running. In general anatomical muscle contraction, nerve signals, orthe like, all of which categorize neural input in general, to controleccentric, concentric, or isometric motions may be used to alter thestate of the damper system during use to optimize safety, symmetry, andbiomechanical movement. This may come about through surface or implantedmyoelectric-like devices, pattern recognition systems, or any other formof neural input to the device. Still furthermore, the use of a graphicsuser interface (GUI) may be used to best characterize the form of neuralinput or equivalent to be best tailored to the prosthetic, orthotic, orrobotic output.

Furthermore, invention 10 may be used in conjunction with an orthoticdevice for a user who has lost the ability to actively plantarflexand/or dorsiflex their natural foot. It is contemplated that invention10 dampening system 18, sensor system 22, microprocessor unit 172 and/orother elements or combinations thereof device may be located on themedial and/or lateral side of an orthotic brace and would controlplantarflexion and dorsiflexion in a similar manner as is describedabove. Still furthermore, dampening system 18 may be usedprosthetically, orthotically, or robotically to control and manage otherjoints such as knee, hip, elbow, and the like.

Still furthermore, it is contemplated to provide an energy returnadjustable heel height prosthetic foot. In a preferred embodiment, amanual or electronic lock may control the dampening system 18 to adjustheel height. It is contemplated that this embodiment may not necessarilyrequire sensory feedback system 22 or microprocessor unit 172 but mayuse the dampening system 18 to manually lock the ankle joint assembly 16at a given angle to provide a user adjustable varied heel height foot.Furthermore, the mechanical components described, in general, may beused with less electronics to provide a simpler functioning, or simplercontrol technique of a largely mechanical system. Furthermore, thedampening system 18 may be altered to be an ankle unit only, with nokeel, in order to be attached to other keel designs, or prosthetic feetin general.

Accordingly, other implementations are within the scope of the followingclaims. Changes may be made in the combinations, operations, andarrangements of the various parts and elements described herein withoutdeparting from the spirit and scope of the invention.

Still furthermore, the disclosed invention, incorporating foot/ankle,knee, and/or hip joints may be used in combination with not onlyprosthetics, orthotics, and robotics devices, but may be used to allowan able-bodied person to ambulate through mechanisms that preventmovement in their own limbs and rely on the functions of the saiddevice.

Knee and Hip Mechanisms

The control and function of a prosthetic knee or hip may be operatedfrom similar information as the ankle device, and may incorporateinformation from the ankle such as but not limited to angle, force,angle of given force, terrain, speed, angular velocity, angularacceleration, force feedback, valve position, strain gauge, sensor,timing, defining point initiation, and other types of information,including any form of neural input, to control the functions of such adevice, in both active powered and resistive manners.

The knee or hip mechanisms may work independently from functions of theankle device, or may utilize data from the ankle to provide functions ofthe knee and/or hip. This may be important whereas if communication islost between the knee and ankle for instance, the knee's functionsshould remain stable for the user, but may be enhanced when incombination with sensor data from the ankle. The described illustrationsshould not be considered limiting in any way and are used forillustrative purposes for those skilled in the art. It is contemplatedthat numerous methods of illustration are conceivable.

For the purposes of explanation, a computer controlled knee workingindependently from any information from the ankle device may functionaccording to:

-   -   Stance Flexion=when angle change in flexion direction, and force        above threshold, GUI setting.    -   Stance Extension=angular change in extension, and force greater        than threshold, then GUI setting.    -   Swing Flexion=force less than threshold, then GUI setting.    -   Swing Extension=force less than threshold, and angle change in        extension direction, the GUI setting.

It should be understood that the term GUI setting may include angularchange, angular velocity, force resistance, speed, movement in general,valve placement, etc., and should not be considered limiting. This maycorrespond to a predetermined or pre-set variable in movementparameters. This would be equivalent for all such knee or hip equations.While the knee is illustrated in these equations, similar orcomplimentary equations may be used for hip movement, while maintainingnecessary variable alterations according to the hip's specific movementduring ambulation and other activities. The GUI setting may furthermorebe predetermined range of values, whereas the amount of resistance orother variable may change in relation to other variables. For instance,as the angle changes, the valve may close to provide increasedresistance to limit the amount of angular velocity with respect to kneeangle.

Additionally, functions such as preventing the knee or hip from bendingfaster than a certain degrees per second may be implemented as a safetyfactor, whereas the valve continually closes corresponding to forces tomaintain an angular velocity above a set threshold. This may be providedas a GUI setting in and of itself.

In a preferred embodiment, the goal of the system may be to maintain aconstant, or correspondingly different from constant angular velocity.As force may increase, and knee is bending, valve position may close forinstance to maintain a constant angular velocity. Alternatively, it maybe desired to allow the knee to bend at slightly faster or slowerangular velocities corresponding to knee angle and forces.

These above equations may also include force value from strain gauges orother sensors to control valve placement or angular velocity of thesystem. This may include a linear or non-linear equation to correspondforce to GUI setting alteration.

Additionally, as speed may increase, may alter the valve placement toalter the angular velocity, and pendular, and dynamic characteristics ofthe knee (and hip). Speed may functionally be correlated to force forcertain activities. These equations may as well include functionscorresponding to force changes, speed changes, terrain changes, and havelearning algorithms associated with them.

Additionally, if system is able to communicate with the ankle forinstance, then the below equations may express possible control functionparameters, however, they are not intended to be limiting in any way. Itis understood that many of the variables, equations, methods, and other,that the ankle joint may utilize or characterize, may be equivalentlyimplemented into other joints such as but not limited to the knee andhip.

STANCE EXTENSION may be minimal resistance at pre-set GUI setting inextension direction only, or may be altered with respect to the heelstrike or foot flat to toe off valve placement settings equation for theankle, and force may be greater than a given threshold.

Stance extension may be defined by foot flat having occurred. Stanceextension may be characterized further as being a pre-set or variablyadjusted angle range. For instance, it may be defined as from 15 degreesof knee flexion to full extension. For the range of 180 degrees offlexion (or full flexion) to that set 15 degrees of flexion, theresistance may be set at a different amount, or may be near zero in theextension direction only. This may as well be altered corresponding tosensor information from the foot.

STANCE FLEXION may be characterized by heel strike having occurred atthe foot and for force to be greater than a given threshold at the footor knee or hip. Resistance may be altered through the equation: averageangular velocity experienced from heel strike to current up to foot flatminus average angular velocity historically from heel strike to footflat, multiplied by a multiplying factor of N4 degrees per X4 degreesper second, then added to the GUI valve placement at heel strike. Thisis from the ankle equations. Furthermore, the angle of the knee may becorresponding to the ankle equation for angle with respect to terrain,and may utilize the variables ((foot flat angle experienced minus footflat angle level ground)+midstance GUI setting). Still furthermore,stance flexion may be further defined by pre-set, or moving according tosensor information, angle range. For instance, stance flexion may befrom full extension to having say 15 degrees of knee flexion. This valueis not meant to be limiting but is meant for illustrative purposes only.Stance flexion past this set or moving value (say from 15 to 180degrees) may be characterized by force greater than threshold, and kneeangle greater than GUI set stance flexion angle. The resistance may aswell be altered with respect to heel strike or foot flat to toe offvalve position setting equation from the ankle. This approach may alsoutilize its own N/X multiplying value.

SWING FLEXION may be characterized by toe off having occurred at thefoot, and force being less than a threshold at the foot or knee or hip.Also may alter resistance according to the heel strike or foot flat totoe off valve placement equation from the ankle device. Swing flexionmay be characterized further as being a pre-set or variably adjustedangle range. For instance, it may be defined as from full extension totwenty-five degrees of flexion. This may as well be alteredcorresponding to sensor information from the foot. Additionally, theremay an additional range where past a set angle value, the resistance maychange again to provide smoother transitions and gait overall.

SWING EXTENSION may be characterized by force being less than thresholdon the ankle, and an angular change in the extension direction of theknee. Swing extension may be characterized further as being a pre-set orvariably adjusted angle range. For instance, it may be defined as fromtwenty-five degrees of flexion to full extension. Additionally, it maybe determined that so long as force is below a threshold, and the limbis moving in the extension direction, the dynamics may be controlled ina given manner through valve placement or similar equation. This may aswell be altered corresponding to sensor information from the foot.Additionally, there may an additional range where past a set anglevalue, the resistance may change again to provide smoother transitionsand gait overall.

Still furthermore, FIG. 50 illustrates a general depiction of resistancevariables in knee mechanism. It should be understood again that the hipjoints movements may similarly correspond, though customized for theknee joints movements. It is conceivable that the resistance values, orangular velocity, or other variables may be maintained as constant 602,or may be varied according to other sensor data 601. Additionally, itshould be understood that FIG. 22 is meant for explanatory purposes onlyand should not be considered as limiting in any way. Still furthermore,the knee or hip joint movements may correspond in some manner to themovement, sensor data, functions, or other, of the ankle joint.

Mesofluidics

It is contemplated as well that through using powered actuationstrategies, the ankle, knee, and hip angle, force, and direction ofmovement, amongst other variables, may be altered in various other waysto provide proper positioning corresponding to the traversedenvironment. Sensor information from the foot, or other joints, orneural control input strategies, as well may be used to govern thenecessary movement of each joint, and may be used to actively power thedevice to perform work. An example of this is allowing a prostheticsystem for instance to lift a user up a flight of stairs.

Mesofluidic actuators are fluid-based actuators that range from a fewmillimeters to centimeters in size and use pressurized fluid for themotive force. Mesofluidics provide high force density (greater than 1000psi), low friction, direct drive, high mechanical bandwidth and canutilize a variety of working fluids ranging from oil to water or salinesolution.

Comparisons of actuation technologies show the many advantages ofhydraulic actuation, specifically mesofluidics, over electromagnetic forhigh-payload robotics applications. One of the main reasons whyhydraulics (versus electric actuators) stems from the observation thatthe power density of hydraulic actuators is approximately five timesgreater than electric drives. Other benefits are fast response (highdynamic bandwidth), small packaging volume (i.e., power to volume ratiotypically 5 to 10 times that of an electric system), and load holdingcapabilities, as well as inherent compliance.

It should be pointed out that hydraulic actuators are fundamentallydifferent than electric motors in that they have no limitationsanalogous to the thermal (due to I2R losses) limitations associated withelectric motors since the hydraulic fluid cools and lubricates thesystem. The amount of flow into a hydraulic actuator is limited only bythe maximum amount of flow possible from the pumping source and any flowrestrictions caused by the flow control elements such as servo valvesand component material pressure limitations. On the other hand, electricmotors are low force, high-speed systems that require some form oftransmission to move a mechanical load, which further increases theoverall weight and size of the actuation system. The force or torquethat can be produced by hydraulic actuators can typically be easilymatched to the application simply by changing the effective area for alinear actuator or the effective displacement for a rotary actuator.Therefore, a transmission system is typically not required for ahydraulic system. As mentioned before, the overall robustness to shockloads is extremely good for hydraulic components.

The disclosed invention may utilize mesofluidic actuation strategies,along with its associated control program technology, to provide aprosthetic system with active power actuation, augmented actuation, orother types or combinations of actuations strategies.

Furthermore, with using active powered joints in real-time during stanceand swing characteristics, associated sensor technology may be used,including but not limited to the position of the device in relation tothe environment, the angle of the device with respect other joints orthe environment, the direction of gravity, force, angle, or othersensors, calculated information based off of sensors, comparison ofsensor data to software or the like to determine defining moments duringthe gait cycle, other calculated information such as through usinggeometry or mathematics to determine relative distance of the devicefrom the environment based off of joint angle sensors, or the like.

Another Preferred Embodiment

Referring to FIG. 46 an ankle joint may generally rotate about a joint701. Such joint may generally provide a separate axis for an anteriorsection of foot 702 and a posterior section of foot 703. Each anteriorand posterior section may independently rotate about a single ormultiple joints. Their respective rotation may be indirectly linkedtogether such as that the anterior section of foot 702 and the posteriorsection of foot 704 may exhibit asymmetrical rotation from one another.

The anterior and posterior sections of the foot may be independentlylinked to a common central axis 704. Such linkages 705 and 706 mayutilize any number of materials or methods, but in a preferredembodiment, it may use a flexible member such as but not limited to atype of webbing, cable, vecran, or categorically similar materials. Suchlinkages 705 and 706 may be attached to the common central axis 704 inindependent areas, each constituting different effective rotationalcharacteristics, such as but not limited to cam shapes or varying radii.

As weight may be applied to the posterior section of foot 703, it maycause such section to move upward with respect to its axis 704. Throughthe linkages, the anterior section of foot 702 may be simultaneouslymoved downward with respect to its axis 704. The linkages may eachgenerally rotate around the central axis in their respective positionsas such section rotates. As linkage 705 and 706 may each be positionedon such central axis 704 in a way as to provide distinct rotationalcharacteristic, the anterior section of foot 702 may generally rotatethrough a different range of motion than the posterior section of foot703 as one of the sections of the foot exhibits forces causing itsrotation.

By doing so, heel strike for instance may initiate a generalplantarflexion moment of the system, and may allow the anterior sectionof foot 702 to for instance have a greater range of motion than theposterior section of foot 703 from heel strike through foot flat. Thismay result in quicker anterior stability of the foot, which may beadvantageous for amputees using such a device, by increasing kneestability.

A spring element 711 may be positioned in line with at least one of thelinkages or other components, allowing for energy to be stored in thesystem at certain times when load is applied. Such spring element 711may be sufficiently strong enough to ensure that it is only loadedduring certain times of the gait cycle, and therefore usedadvantageously for its purpose. It is understood that spring element(s)711 may be positioned in any number of locations along the system,including in line with the linkages 705 and or 706, within the anterioror posterior sections 702 and or 703, or within the central axis 704,amongst others.

Central axis 704 may generally be connected to bracket 707, which maygenerally mount to a connection point 708 to attach to the prosthetic.As illustrated in FIG. 47, central axis 704, not drawn to optimizedsizing, scale, or shape characteristics, generally illustrates oneembodiment of how one may achieve asymmetrical dynamics of the anteriorand posterior sections through offering varying diameters of the centralaxis.

In such a system, anterior section of foot 702 and posterior section offoot 703 may be able to utilize rigid elements as opposed toconventionally used flexible elements, although flexible elements may beused instead. If rigid elements are used, it may allow for a lighterweight device, while maintaining sufficient strength and durability. Forinstance square stock, tubing, U channel, or the like may be usedinstead of conventionally used struts, which slightly bend, and maybreak if excessive load is applied. If U channel may be used, it mayallow for rotational flexibility, while maintaining excellent strengthin a bending moment.

Such anterior sections and posterior sections may generally be connectedto base sections 709 and 710. Such sections may be pivoted, or rigidlyconnected, and may generally provide slight ground compliance. Ifanterior base section 709 can be pivoted, it may allow for thefunctional equivalent of forefoot flexion (bending of the toes) duringlate stance phase, while simultaneously loading the spring element(s)711.

During the gait cycle, the central axis 704 may be locked, ortransitioned toward a locked position, at various instances in order toprovide biomechanical symmetry with the user. Various types of lockmechanisms may be used to prevent rotation of the central axis 704, andhence prevent movement of the anterior section of foot 702 and posteriorsection of foot 703. While such central axis 704 may generally be in alocked position, an in-line spring or energy storing element 711 maybecome engaged to store energy, which may be released at another timeduring the gait cycle.

The central axis 704 shape may include cam shapes, asymmetrical shapes,and varying sizes of various shapes to enable the anterior and posteriorlinkages and their corresponding anterior and posterior sections to havediffering amounts of movement and or rotational change with respect toeach other. For instance, the posterior linkage may wrap around asmaller diameter cylinder section of the central axis 704 whereas theanterior linkage may wrap around a larger diameter cylinder section ofthe central axis, whereby causing the two to have differing amounts ofangular change from each other.

During the gait cycle, the central axis 704 may be locked, ortransitioned toward a locked position, at various instances in order toprovide biomechanical symmetry with the user. Various types of lockmechanisms may be used to prevent rotation of the central axis 704, andhence prevent movement of the anterior section of foot 702 and posteriorsection of foot 703. While such central axis 704 may generally be in alocked position, an in-line spring or energy storing element 711 maybecome engaged to store energy, which may be released at another timeduring the gait cycle.

Heel strike: The central axis lock mechanism (not shown in thesimplified illustration) may generally allow for controlledplantarflexion of the ankle.

Foot flat: The central axis may transition to becoming locked at or at acontrolled angular (or other) change after foot flat is achieved. Footflat may be defined by an angular change from plantarflexion todorsiflexion angle during the gait cycle. Energy storage may begin at ornear this portion of the gait cycle, once the central axis becomeslocked, and the angle may be changing during roll over. Such anglechange may come about through an energy storage mechanism, versusthrough axis angle change alone.

Midstance: The central axis may transition to becoming locked at or at acontrolled angular (or other) change at or near midstance. This may be adefined moment past foot flat.

Heel off: This may be a defined moment past midstance, and may generallyallow for the toe section to continue to load the energy storingelement.

Toe off: This may be a defined moment and may initiate the lockmechanism to be released at or just before, in order to provide energyback to the user during the final portion of the stance phase.

Control of such lock mechanism, and determination of defining momentsand gait cycle moments may come about through computer controlled means,or may come about mechanically, or a combination thereof. For instance,the determination of heel strike may come about through sensor data suchas looking at an angular change in the plantarflexion direction, a forcesensor, or others, which may tell a computer to engage an actuated lockmechanism. Likewise, heel strike force or angular change of the unit maymechanically engage a lock mechanism to accomplish the same, without theuser of a computer. Such control program may be accomplished inprinciple with similar means, although the tool set to accomplish suchmechanisms may differ. The characteristics of such a central axis may beadjustable by the end user or practitioner to enable for customizedasymmetrical (or symmetrical) characteristics of the dynamics of theanterior section and posterior section of the foot.

It is understood that invention 700 may consist of various embodimentsdeparting from those shown, and those shown should not be consideredlimiting. In one embodiment, such central axis lock mechanism mayutilize principles from a common seat belt unit to provide the locking.This may be initiated mechanically or electronically.

Likewise, in another embodiment, such central axis lock mechanism mayutilize principles from brakes, such as but not limited to pad or discbrakes. This may utilize common parts, or modified designs of parts,from bicycles, motorcycles, automobiles, or other machinery brakingmechanisms. In the instance of using parts from bicycles, a unit may becreated whereas common bike parts may be used to fabricate or repairsuch an ankle mechanism.

In common bike disc brake units, as illustrated in FIGS. 48 and 49, thebrake is initiated through a mechanical hand lever, which may close thebrake unit mechanically or hydraulically. Using such an example, thefunctional equivalent of the hand brake mechanism from a bike may beinitiated through weight bearing onto the device, or may become engagedthrough the plantarflexion moment or movement that occurs at or afterheel strike, or may be initiated through electronic and or sensor input,with or without an actuator. For instance, an electronic sensor mayinitiate a small actuator, which may allow a mechanical loading of thefunctional equivalent of a hand brake unit to engage the disc brake. Bydoing such, intelligent control may be used for the exact timing and ordynamics of how the brake may be engaged, but the force to close such abrake could come about through actual body weight dynamics, versusrelying on a considerably larger actuator than would be used otherwise.If just a small actuator is used to engage or enable the body weight toactually lock out the brake, it could be considerably more energyefficient.

At least a portion of such a disc brake may be utilized within the spaceof a prosthetic device, as the unit would likely not rotate multiplerevolutions as would occur in a bike example, and likely would notrotate past a few degrees in total. Further, the sizing, positioning,and mechanical gearing of such a system may such that it optimizes thefunction of such a system for use in a prosthetic or orthotic device.Such approach for a locking or actuator mechanism for a prosthetic ororthotic device would enable the unit to be comparably lightweight,small, robust, and field serviceable.

It is understood that as an actuator or lock mechanism, it may beequally beneficial as used in a knee joint as in an ankle joint.Likewise, because of its low profile shape, it may be especiallyadvantageous as used in orthotic devices. The use of such a systemshould not be considered limited to a prosthetic ankle.

Such brake lock mechanism may be integrated within central axis area ofthe device. In an alternative embodiment as generally illustrated inFIG. 50, central axis may incorporate an energy storing mechanism withinits design. In such an example, though not drawn to optimizedcharacteristics, an energy storing spring, or other such energy storingmechanism may be integrated. Such figure should not be consideredlimiting, as such illustration is purposely over simplified forillustrative purposes, and such embodiment could be configured in anumber of methods.

Incorporated in any area of the device may be a spring element, whichmay cause the device to move into general dorsiflexion during the swingphase of gait. When load is not applied on the unit, and when the lockmechanism is not engaged, the spring element may be stronger than theinertial and static friction forces of the unit, thereby causing it tomove into dorsiflexion.

I claim:
 1. A prosthetic ankle comprising: a frame; a computer incommunication with said frame; a damping device in communication withsaid computer and said frame; a joint connected to said frame; a sensorfor sensing plantarflexion moment information and dorsiflexion momentinformation in communication with said computer; wherein said jointprovides at least one axis of rotation about said prosthetic ankle andwherein said damping device facilitates resistance to said at least oneaxis of rotation; and wherein said computer determines said resistanceto said at least one axis of rotation with said plantarflexion momentinformation and said dorsiflexion moment information.